Protein-resistant articles comprising cyclobutanediol

ABSTRACT

This invention relates to a medical device comprising a UV-cured silicone polymer coating on at least a portion of a surface of the device and at least one polyester composition comprising a cyclobutanediol and methods for making the medical device.

CROSS-REFERENCE TO RELATED APPLICATION

This application claims priority under 35 U.S.C. § 119(e) to U.S.Provisional Patent Application No. 60/642,622, filed on Jan. 10, 2005,U.S. Provisional Application Ser. No. 60/691,567 filed on Jun. 17, 2005,U.S. Provisional Application Ser. No. 60/731,454 filed on Oct. 28, 2005,U.S. Provisional Application Ser. No. 60/731,389, filed on Oct. 28,2005, U.S. Provisional Application Ser. No. 60/739,058, filed on Nov.22, 2005, and U.S. Provisional Application Ser. No. 60/738,869, filed onNov. 22, 2005, U.S. Provisional Application Ser. No. 60/750,692 filed onDec. 15, 2005, U.S. Provisional Application Ser. No. 60/750,693, filedon Dec. 15, 2005, U.S. Provisional Application Ser. No. 60/750,682,filed on Dec. 15, 2005, and U.S. Provisional Application Ser. No.60/750,547, filed on Dec. 15, 2005, all of which are hereby incorporatedby this reference in their entireties.

FIELD OF THE INVENTION

The invention generally relates to protein-resistant articles, includingmedical devices, comprising a polyester comprising a cyclobutanediol.More particularly the present invention generally relates to proteinresistant articles, including medical devices, comprising a UV-curedsilicone polymer coating composition and a polyester made fromterephthalic acid or an ester thereof, or mixtures thereof,2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 1,4-cyclohexanedimethanol,the polyester having a certain combination of inherent viscosity andglass transition temperature (Tg). These medical devices are believed tohave a unique combination of at least one of high impact strengths, highglass transition temperature (T_(g)), low ductile-to-brittle transitiontemperatures, good color and clarity, low densities, and longcrystallization half-times, which allow them to be easily formed intoarticles. The invention also relates to a method for reducinginteraction between the cyclobutanediol containing, protein resistantarticles and a biological fluid or system.

BACKGROUND OF THE INVENTION

This invention pertains to the improvement of protein resistance andbiocompatibility of articles that come into contact with biologicalsystems, through the application of biocompatible coatings. Thesecoatings have uses in many different areas in which the adsorption ofproteins may be problematic, such as diagnostic tests in whichquantification of the amount of proteins in a sample may be complicatedby adsorption of proteins at the surface of a medical device, as well asoperations in which the buildup of proteins can prevent properoperation, such as filtration apparatus. Additionally, the importance ofbiocompatible articles arises in part from their utility in medicaldevices. The term “medical device,” as used herein, describes anapparatus that is used in the diagnosis or treatment of a disease andthat come into contact with biological materials, including tissue,blood, or other biological fluids, from animals, humans or plants. Theterm ‘biocompatible’ is used herein to describe the effect ofsubstantially reducing by greater than about 50%, preferably greaterthan about 80%, more preferably by greater than about 90% or minimizingor eliminating completely the interaction between a biological systemand the introduced foreign surface. The term “protein-resistant” is usedherein to describe a reduced tendency to adsorb protein compared to anuncoated surface or article.

Though a material used for a particular application might have lowreactivity, low levels of extractable substances, and/or be otherwiseinert, biological systems may have adverse reactions to the introductionof such a foreign surface. This is due to the interaction of proteinswith the foreign surface. It is accepted that the first observable eventto occur when a foreign surface contacts a biological system is theadsorption of proteins, and this adsorption can dictate the type andextent of the response to that surface. (J. D. Andrade and V. Hlady,Protein Adsorption and Materials Biocompatibility: A Tutorial Review andSuggested Hypotheses, in Advances in Polymer Science, 79, (1986), p. 3;L. Vroman and A. L. Adams, Journal of Biomedical Materials Research, 3,(1969), p. 43.)

One approach to overcoming any negative effects associated with thecontact of a surface with a biological system is to form the entirearticle out of a biocompatible material. While several materials havebeen identified as biocompatible, these materials may not possess all ofthe other necessary properties to be successfully employed. Theparticular needs of an application may dictate that a particular articlebe formed of materials with specific characteristics, examples of whichare physical properties such as stiffness or optical clarity.

Poly(1,4-cyclohexylenedimethylene)terephthalate (PCT), a polyester basedsolely on terephthalic acid and 1,4-cyclohexanedimethanol, is known inthe art and is commercially available. This polyester crystallizesrapidly upon cooling from the melt, making it very difficult to formamorphous articles by methods known in the art such as extrusion,injection molding, and the like. In order to slow down thecrystallization rate of PCT, copolyesters can be prepared containingadditional dicarboxylic acids or glycols such as isophthalic acid orethylene glycol. These ethylene glycol- or isophthalic acid-modifiedPCTs are also known in the art and are commercially available.

One common copolyester used to produce films, sheeting, and moldedarticles is made from terephthalic acid, 1,4-cyclohexanedimethanol, andethylene glycol. While these copolyesters are useful in many end-useapplications, they exhibit deficiencies in properties such as glasstransition temperature and impact strength when sufficient modifyingethylene glycol is included in the formulation to provide for longcrystallization half-times. For example, copolyesters made fromterephthalic acid, 1,4-cyclohexanedimethanol, and ethylene glycol withsufficiently long crystallization half-times to provide for amorphousproducts exhibiting higher ductile-to-brittle transition temperaturesand lower glass transition temperatures than the compositions revealedherein.

The polycarbonate of 4,4′-isopropylidenediphenol (bisphenol Apolycarbonate) has been used as an alternative for polyesters known inthe art and is a well known engineering molding plastic. Bisphenol Apolycarbonate is a clear, high-performance plastic having good physicalproperties such as dimensional stability, high heat resistance, and goodimpact strength. Although bisphenol-A polycarbonate has many goodphysical properties, its relatively high melt viscosity leads to poormelt processability and the polycarbonate exhibits poor chemicalresistance. It is also difficult to thermoform.

Polymers containing 2,2,4,4-tetramethyl-1,3-cyclobutanediol have alsobeen generally described in the art. Generally, however, these polymersexhibit high inherent viscosities, high melt viscosities and/or high Tgs(glass transition temperatures) such that the equipment used in industryis insufficient to manufacture or post polymerization process thesematerials.

Thus, there is a need in the art for medical devices comprising at leastone polymer with a unique combination of properties, such as toughnessand high glass transition temperature of polycarbonate but with thehydrolytic stability, chemical resistance, lower density and/orthermoformability of polyesters while retaining processability on thestandard equipment used in the industry.

SUMMARY OF THE INVENTION

The present inventors have adopted the approach of modifying the surfaceof a material having suitable bulk properties to improvebiocompatibility. In particular, the present inventors have adopted theapproach of applying a coated layer of a more biocompatible materialover another material with the appropriate physical properties. Thissurface modification is also applied to polyester compositionscomprising a cyclobutanediol.

The present invention is directed to an ultraviolet light (UV)-curable,silicone-based coating, on at least a portion of a surface of a medicaldevice comprising a polyester comprising a cyclobutanediol, whichimproves protein resistance and biocompatibility, may be coated onvarious substrates, and overcomes several difficulties identified inpreviously disclosed methods.

It is believed that certain articles, including medical devices,comprising polyesters made from terephthalic acid, an ester thereof, ormixtures thereof, 1,4-cyclohexanedimethanol and2,2,4,4-tetramethyl-1,3-cyclobutanediol with a certain combination ofinherent viscosity and glass transition temperatures are superior topolyesters known in the art and to polycarbonate with respect to atleast one of hydrolytic stability, toughness, chemical resistance, lowerspecific gravity, and thermoformability. These medical devices arebelieved to be similar to polycarbonate in heat resistance and are stillprocessable on the standard industry equipment.

In one aspect, the invention provides a protein-resistant medical devicethat comprises a UV-cured silicone polymer coating on at least a portionof the surface thereof.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.10            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from 85 to            200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,    -   (c) residues of at least one branching agent;        wherein the total mole % of the dicarboxylic acid component is        100 mole %, and the total mole % of the glycol component is 100        mole %; and        wherein the inherent viscosity of the polyester is from 0.35 to        1.2 dL/g as determined in 60/40 (wt/wt)phenol/tetrachloroethane        at a concentration of 0.5 g/100 ml at 25° C.; and wherein the        polyester has a Tg of 85 to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 80 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 20 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 85° C. to            200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 80 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 20 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 125 to 200°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 85 to 200°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 55 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 45 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; wherein the polyester has a Tg of 85 to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 50 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 50 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; wherein the polyester has a Tg of 85 to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 45 to 55 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 45 to 55 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; wherein the polyester has a Tg of 85 to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) greater than 50 up to 99 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 1 to less than 50 mole % of 1,4-cyclohexanedimethanol            residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from 85 to            200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) greater than 50 up to 80 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 20 to less than 50 mole % of 1,4-cyclohexanedimethanol            residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from 85° C.            to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) greater than 51 up to 80 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 20 to less than 49 mole % of 1,4-cyclohexanedimethanol            residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from 85° C.            to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,    -   (c) residues of at least one branching agent;        wherein the total mole % of the dicarboxylic acid component is        100 mole %, and the total mole % of the glycol component is 100        mole %; and        wherein the inherent viscosity of the polyester is from 0.35 to        1.2 dL/g as determined in 60/40 (wt/wt)phenol/tetrachloroethane        at a concentration of 0.5 g/100 ml at 25° C.; and wherein the        polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) greater than 50 up to 99 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 1 to less than 50 mole % of 1,4-cyclohexanedimethanol            residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from            110° C. to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) greater than 51 up to 99 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 1 to less than 49 mole % of 1,4-cyclohexanedimethanol            residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from            110° C. to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) greater than 50 up to 80 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 20 to less than 50 mole % of 1,4-cyclohexanedimethanol            residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from            110° C. to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) greater than 51 up to 80 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 20 to less than 49 mole % of 1,4-cyclohexanedimethanol            residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from            110° C. to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from 110 to            300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 80 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 20 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 110 to 300°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 110 to 300°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 55 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 45 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; wherein the polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 50 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 50 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; wherein the polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 45 to 55 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 45 to 55 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; wherein the polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 80 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 20 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 110 to 300°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            and less than 0.70 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from 110 to            300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is greater            than 0.76 up to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from            110° C. to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) comprising at least one polyester composition comprising at        least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 110 to 150°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 110 to 150°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 120 to 135°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 120 to 135°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from            127° C. to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 80 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 20 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 127° C. to            200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from            greater than 148° C. up to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from            greater than 148° C. up to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 64.9 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 59.9 mole % of 1,4-cyclohexanedimethanol residues,        -   iii) 0.10 to less than 15 mole % ethylene glycol residues;            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; wherein the polyester has a Tg of 85 to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.;            wherein the polyester has a Tg of 85 to 200° C. and            optionally, wherein one or more branching agents is added            prior to or during the polymerization of the polymer.

In one aspect, this invention relates to a medical device comprising:

(I) a UV-cured silicone polymer coating on at least a portion of asurface of the device; and

(II) at least one polyester composition comprising at least onepolyester which comprises:

-   -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues;            and            (III) at least one thermal stabilizer;            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40            (wt/wt)phenol/tetrachloroethane at a concentration of 0.5            g/100 ml at 25° C.;            wherein the polyester has a Tg of 85 to 200° C.

In one aspect, this invention relates to a medical device comprising

(I) a UV-cured silicone polymer coating on at least a portion of asurface of the device; and

(II) at least one polyester composition comprising at least onepolyester which comprises:

-   -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues;            and            (III) at least one thermal stabilizer and/or reaction            product(s) thereof;            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40            (wt/wt)phenol/tetrachloroethane at a concentration of 0.5            g/100 ml at 25° C.;            wherein the polyester has a Tg of 85 to 200° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 64.9 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 59.9 mole % of 1,4-cyclohexanedimethanol residues,        -   iii) 0.10 to less than 15 mole % ethylene glycol residues;            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g or less as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; wherein the polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.;            wherein the polyester has a Tg of 110 to 300° C. and            optionally, wherein one or more branching agents is added            prior to or during the polymerization of the polymer.

In one aspect, this invention relates to a medical device comprising

(I) a UV-cured silicone polymer coating on at least a portion of asurface of the device; and

(II) at least one polyester composition comprising at least onepolyester which comprises:

-   -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues;            (III) at least one thermal stabilizer;            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40            (wt/wt)phenol/tetrachloroethane at a concentration of 0.5            g/100 ml at 25° C.;            wherein the polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising:        (I) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues;            and            (II) at least one thermal stabilizer and/or reaction            products thereof;            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40            (wt/wt)phenol/tetrachloroethane at a concentration of 0.5            g/100 ml at 25° C.;            wherein the polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising:        (I) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 64.9 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 59.9 mole % of 1,4-cyclohexanedimethanol residues,        -   iii) 0.10 to less than 15 mole % ethylene glycol residues;            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 0.75 dL/g or less as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; wherein the polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.;            wherein the polyester has a Tg of 110 to 300° C. and            optionally, wherein one or more branching agents is added            prior to or during the polymerization of the polymer.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,    -   (c) residues of at least one branching agent;        wherein the total mole % of the dicarboxylic acid component is        100 mole %, and the total mole % of the glycol component is 100        mole %; and        wherein the inherent viscosity of the polyester is from 0.35 to        1.2 dL/g as determined in 60/40 (wt/wt)phenol/tetrachloroethane        at a concentration of 0.5 g/100 ml at 25° C.; and wherein the        polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues;            and    -   (c) at least thermal stabilizer and/or reaction products        thereof;        wherein the total mole % of the dicarboxylic acid component is        100 mole %, and the total mole % of the glycol component is 100        mole %; and        wherein the inherent viscosity of the polyester is 0.35 to 1.2        dL/g as determined in 60/40 (wt/wt)phenol/tetrachloroethane at a        concentration of 0.5 g/100 ml at 25° C.;        wherein the polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising:        (I) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues;            and            (II) at least one thermal stabilizer and/or reaction            products thereof;            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40            (wt/wt)phenol/tetrachloroethane at a concentration of 0.5            g/100 ml at 25° C.;            wherein the polyester has a Tg of 110 to 300° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) greater than 40 to 99 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 1 to less than 60 mole % of 1,4-cyclohexanedimethanol            residues;            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.10            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; wherein the polyester has a Tg of 85 to 200° C.;            wherein the polyester is amorphous; wherein if ethylene            glycol residues is present in the glycol component, it is            present in less than 15 mole %.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) an amorphous polyester comprising:    -   (a) a dicarboxylic acid component comprising:        -   i) 90 to 100 mole % of terephthalic acid residues;        -   ii) up to 10 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) up to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) from 10 to 100 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) up to 90 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) an amorphous polyester comprising:    -   (a) a dicarboxylic acid component comprising:        -   i) 90 to 100 mole % of terephthalic acid residues;        -   ii) up to 10 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) up to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) from 25 to 100 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) up to 75 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and wherein the amorphous polyester has a            glass transition temperature (T_(g)) of greater than 120° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.10 to            less than 1 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from 85 to            120° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from 85 to            120° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from 95° C.            to 115° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 1 to 99 mole % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol            residues; and        -   ii) 1 to 99 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is 0.35 to            less than 1 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of from 95° C.            to 115° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 5 to less than 50 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 50 to 95 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and            wherein the polyester has a Tg of 85 to 120° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 10 to 30 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 70 to 90 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and            wherein the polyester has a Tg of 85 to 120° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 15 to 25 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 75 to 85 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity is from 0.50 to 1.2 dL/g as            determined in 60/40 (wt/wt) phenol/tetrachloroethane at a            concentration of 0.5 g/100 ml at 25° C.; and            wherein the polyester has a Tg of 85 to 120° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 5 to less than 50 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 50 to 95 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 95 to 115°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 10 to 30 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 70 to 90 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 95 to 115°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 15 to 25 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 75 to 85 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 95 to 115°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) comprising at least one polyester composition comprising at        least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 5 to less than 50 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 50 to 95 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to less than 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 85 to 120°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 10 to 30 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 70 to 90 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to less than 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 85 to 120°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 15 to 25 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 75 to 85 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to less than 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 85 to 120°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) comprising at least one polyester composition comprising at        least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 5 to less than 50 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 50 to 95 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to less than 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 95 to 115°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 10 to 30 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 70 to 90 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to less than 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 95 to 115°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 15 to 25 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 75 to 85 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to less than 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 95 to 115°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 15 to 25 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) greater than 75 to 85 mole % of            1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.6            to 0.72 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 95 to 115°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to less than 5 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) optionally, 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 4.5 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) optionally, 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 4 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) optionally, 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 3 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 2.0 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) optionally, 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 1 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to less than 1 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 15 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 15 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) 70 to 99.08 mole % ethylene glycol residues, and        -   iii) 0.01 to 15 mole % of 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 10 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 10 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) 80 to 99.08 mole % of ethylene glycol residues, and        -   iii) 0.01 to 10 mole % of 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 5 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to less than 5 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 4.5 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 4 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 3 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 60 to 110°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 2.0 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 85 to 200°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to 1 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 85 to 200°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester composition comprising at least one        polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 0.01 to less than 1 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues;        -   ii) ethylene glycol residues, and        -   iii) 1,4-cyclohexanedimethanol residues            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.35            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and wherein the polyester has a Tg of 85 to 200°            C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i). 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.5            to 0.68 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %;            wherein the inherent viscosity of the polyester is 0.68 dL/g            or less as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and optionally, wherein one or more branching            agents is added, but when the branching agent is added, it            is added only prior to or during the polymerization of the            polyester.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) from 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            and    -   (c) branching agent residues;        wherein the total mole % of the dicarboxylic acid component is        100 mole %, and the total mole % of the glycol component is 100        mole %; and        wherein the inherent viscosity of the polyester is from 0.5 to        1.2 dL/g as determined in 60/40 (wt/wt) phenol/tetrachloroethane        at a concentration of 0.5 g/100 ml at 25° C. In one embodiment,        the branching agent is added before or during polymerization of        the polymer.

In one aspect, this invention relates to a medical device comprising

(I) a UV-cured silicone polymer coating on at least a portion of asurface of the device;

(II) at least one polyester which comprises:

-   -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            and

(III) at least one thermal stabilizer and/or reaction products thereof;

wherein the total mole % of the dicarboxylic acid component is 100 mole%, and the total mole % of the glycol component is 100 mole %; and

wherein the inherent viscosity of the polyester is from 0.5 to 1.2 dL/gas determined in 60/40 (wt/wt) phenol/tetrachloroethane at aconcentration of 0.5 g/100 ml at 25° C.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) from 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and            wherein the polyester has a Tg of 110 to 160° C. or 110 to            150° C. or 120 to 160° C. or 120 to 150° C. or 120 to            135° C. or 130 to 145° C., as well as other glass transition            temperatures (Tgs) described herein, as measured by a TA DSC            2920 from Thermal Analyst Instrument at a scan rate of 20°            C./min.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to 0.75 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and            wherein the polyester has a Tg of 110 to 160° C. or 110 to            150° C. or 120 to 160° C. or 120 to 150° C. or 120 to            135° C. or 130 to 145° C., as measured by a TA DSC 2920 from            Thermal Analyst Instrument at a scan rate of 20° C./min.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) from 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to 0.72 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and            wherein the polyester has a Tg of 110 to 160° C. or 110 to            150° C. or 120 to 160° C. or 120 to 150° C. or 120 to            135° C. or 130 to 145° C., as measured by a TA DSC 2920 from            Thermal Analyst Instrument at a scan rate of 20° C./min.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to 0.68 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and            wherein the polyester has a Tg of 110 to 160° C. or 110 to            150° C. or 120 to 160° C. or 120 to 150° C. or 120 to            135° C. or 130 to 145° C., as measured by a TA DSC 2920 from            Thermal Analyst Instrument at a scan rate of 20° C./min.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) from 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to less than 0.68 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and            wherein the polyester has a Tg of 110 to 160° C. or 110 to            150° C. or 120 to 160° C. or 120 to 150° C. or 120 to            135° C. or 130 to 145° C., as measured by a TA DSC 2920 from            Thermal Analyst Instrument at a scan rate of 20° C./min.

In one aspect, this invention relates to a medical device comprising

-   -   (1) a UV-cured silicone polymer coating on at least a portion of        a surface of the device; and    -   (2) at least one polyester which comprises:    -   (a) a dicarboxylic acid component comprising:        -   i) 70 to 100 mole % of terephthalic acid residues;        -   ii) 0 to 30 mole % of aromatic dicarboxylic acid residues            having up to 20 carbon atoms; and        -   iii) 0 to 10 mole % of aliphatic dicarboxylic acid residues            having up to 16 carbon atoms; and    -   (b) a glycol component comprising:        -   i) 40 to 65 mole % of            2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and        -   ii) 35 to 60 mole % of 1,4-cyclohexanedimethanol residues,            wherein the total mole % of the dicarboxylic acid component            is 100 mole %, and the total mole % of the glycol component            is 100 mole %; and            wherein the inherent viscosity of the polyester is from 0.50            to 1.2 dL/g as determined in 60/40 (wt/wt)            phenol/tetrachloroethane at a concentration of 0.5 g/100 ml            at 25° C.; and            wherein the polyester has a Tg of 120 to 135° C. as measured            by a TA DSC 2920 from Thermal Analyst Instrument at a scan            rate of 20° C./min.

In one aspect, the polyesters useful in the invention contain less than15 mole % ethylene glycol residues, such as, for example, 0.01 to lessthan 15 mole % ethylene glycol residues.

In one aspect, the polyesters useful in the invention contain noethylene glycol residues.

In one aspect the polyester compositions useful in the invention containat least one thermal stabilizer and/or reaction products thereof.

In one aspect, the polyesters useful in the invention contain nobranching agent, or alternatively, at least one branching agent is addedeither prior to or during polymerization of the polyester.

In one aspect, the polyesters useful in the invention contain at leastone branching agent without regard to the method or sequence in which itis added.

In one aspect, the polyesters useful in the invention are made from no1,3-propanediol, or, 1,4-butanediol, either singly or in combination. Inother aspects, 1,3-propanediol or 1,4-butanediol, either singly or incombination, may be used in the making of the polyester of thisinvention.

In one aspect of the invention, the mole % ofcis-2,2,4,4-tetramethyl-1,3-cyclobutanediol is greater than 50 mole % orgreater than 55 mole % of cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol orgreater than 70 mole % of cis-2,2,4,4-tetramethyl-1,3-cyclobutanediol;wherein the total mole percentage ofcis-2,2,4,4-tetramethyl-1,3-cyclobutanediol andtrans-2,2,4,4-tetramethyl-1,3-cyclobutanediol is equal to a total of 100mole %.

In one aspect, the polyester compositions are useful in articles ofmanufacture, such as medical devices, including but not limited to,extruded, calendered, and/or molded articles including but not limitedto, injection molded articles, extruded articles, cast extrusionarticles, profile extrusion articles, melt spun articles, extrusionmolded articles, injection blow molded articles, injection stretch blowmolded articles and extrusion blow molded articles. These articles caninclude, but are not limited to, films, bottles, containers, sheetand/or fibers.

In one aspect, the polyester compositions useful in the invention may beused in various types of film and/or sheet, including but not limited toextruded film(s) and/or sheet(s), calendered film(s) and/or sheet(s),compression molded film(s) and/or sheet(s), solution casted film(s)and/or sheet(s). Methods of making film and/or sheet include but are notlimited to extrusion, calendering, compression molding, and solutioncasting.

Also, in one aspect, use of these particular polyester compositionsminimizes and/or eliminates the drying step prior to melt processingand/or thermoforming.

In one aspect, the polyester compositions are useful in medical devicesincluding but not limited to extruded and/or molded articles includingbut not limited to injection molded articles, extrusion molded articles,injection blow molded articles, injection stretch blow molded articles,extrusion blow molded articles and extrusion stretch blow moldedarticles. These medical devices can include but are not limited tobottles.

In one aspect, the polyesters useful in the medical devices of theinvention may be amorphous or semicrystalline. In one aspect, certainpolyesters useful in the invention can have a relatively lowcrystallinity. Certain polyesters useful in the invention can thus havea substantially amorphous morphology, meaning that the polyesterscomprise substantially unordered regions of polymer.

In another aspect, the invention provides a method for reducinginteraction between a medical device and a biological fluid or system.The method comprises coating at least a portion of a surface of thedevice with a UV-curable silicone polymer composition and exposing atleast a portion of the silicone polymer composition to ultraviolet lightto cure the composition.

The use of a UV-curable silicone polymer coating composition allows forrapid curing, low-temperature curing for temperature-sensitivesubstrates, as well as patterning of the coated substrate.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a graph showing the effect of comonomer on the fastestcrystallization half-times of modified PCT copolyesters.

FIG. 2 is a graph showing the effect of comonomer on thebrittle-to-ductile transition temperature (T_(bd)) in a notched Izodtest (ASTM D256, ⅛-in thick, 10-mil notch).

FIG. 3 is a graph showing the effect of2,2,4,4-tetramethyl-1,3-cyclobutanediol composition on the glasstransition temperature (Tg) of the copolyester.

DETAILED DESCRIPTION OF THE INVENTION

The present invention may be understood more readily by reference to thefollowing detailed description of certain embodiments of the inventionand the working examples. In accordance with the purpose(s) of thisinvention, certain embodiments of the invention are described in theSummary of the Invention and are further described herein below. Also,other embodiments of the invention are described herein.

It is believed that medical devices comprising the polyester(s) havingthe composition(s) described herein having the compositions describedabove have a combination of two or more physical properties such as highimpact strength, moderate glass transition temperatures, chemicalresistance, hydrolytic stability, toughness, low ductile-to-brittletransition temperatures, good color and clarity, low densities, and longcrystallization half-times, good thermoformability, and goodprocessability thereby easily permitting them to be formed intoarticles. In some of the embodiments of the invention, the polyestershave a unique combination of the properties of good impact strength,heat resistance, chemical resistance, density and/or the combination ofthe properties of good impact strength, heat resistance, andprocessability and/or the combination of two or more of the describedproperties, that have never before been believed to be present in apolyester.

The term “polyester”, as used herein, is intended to include“copolyesters” and is understood to mean a synthetic polymer prepared bythe reaction of one or more difunctional carboxylic acids and/ormultifunctional carboxylic acids with one or more difunctional hydroxylcompounds and/or multifunctional hydroxyl compounds. Typically thedifunctional carboxylic acid can be a dicarboxylic acid and thedifunctional hydroxyl compound can be a dihydric alcohol such as, forexample, glycols and diols. The term “glycol” as used in thisapplication includes, but is not limited to, diols, glycols, and/ormultifunctional hydroxyl compounds. Alternatively, the difunctionalcarboxylic acid may be a hydroxy carboxylic acid such as, for example,p-hydroxybenzoic acid, and the difunctional hydroxyl compound may be anaromatic nucleus bearing 2 hydroxyl substituents such as, for example,hydroquinone. The term “residue”, as used herein, means any organicstructure incorporated into a polymer through a polycondensation and/oran esterification reaction from the corresponding monomer. The term“repeating unit”, as used herein, means an organic structure having adicarboxylic acid residue and a diol residue bonded through acarbonyloxy group. Thus, for example, the dicarboxylic acid residues maybe derived from a dicarboxylic acid monomer or its associated acidhalides, esters, salts, anhydrides, or mixtures thereof. Furthermore, asused in this application, the term “diacid” includes multifunctionalacids such as branching agents. As used herein, therefore, the termdicarboxylic acid is intended to include dicarboxylic acids and anyderivative of a dicarboxylic acid, including its associated acidhalides, esters, half-esters, salts, half-salts, anhydrides, mixedanhydrides, or mixtures thereof, useful in a reaction process with adiol to make polyester. As used herein, the term “terephthalic acid” isintended to include terephthalic acid itself and residues thereof aswell as any derivative of terephthalic acid, including its associatedacid halides, esters, half-esters, salts, half-salts, anhydrides, mixedanhydrides, or mixtures thereof or residues thereof useful in a reactionprocess with a diol to make polyester.

In one embodiment, terephthalic acid may be used as the startingmaterial. In another embodiment, dimethyl terephthalate may be used asthe starting material. In yet another embodiment, mixtures ofterephthalic acid and dimethyl terephthalate may be used as the startingmaterial and/or as an intermediate material.

The polyesters useful in the medical devices of the present inventiontypically can be prepared from dicarboxylic acids and diols which reactin substantially equal proportions and are incorporated into thepolyester polymer as their corresponding residues. The polyesters usefulin the medical devices of the present invention, therefore, can containsubstantially equal molar proportions of acid residues (100 mole %) anddiol (and/or multifunctional hydroxyl compound) residues (100 mole %)such that the total moles of repeating units is equal to 100 mole %. Themole percentages provided in the present disclosure, therefore, may bebased on the total moles of acid residues, the total moles of diolresidues, or the total moles of repeating units. For example, apolyester containing 30 mole % isophthalic acid, based on the total acidresidues, means the polyester contains 30 mole % isophthalic acidresidues out of a total of 100 mole % acid residues. Thus, there are 30moles of isophthalic acid residues among every 100 moles of acidresidues. In another example, a polyester containing 25 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol, based on the total diolresidues, means the polyester contains 25 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues out of a total of 100mole % diol residues. Thus, there are 25 moles of2,2,4,4-tetramethyl-1,3-cyclobutanediol residues among every 100 molesof diol residues.

In other aspects of the invention, the Tg of the polyesters useful inthe medical device(s) of the invention can be at least one of thefollowing ranges: 85 to 200° C.; 85 to 190° C.; 85 to 180° C.; 85 to170° C.; 85 to 160° C.; 85 to 155° C.; 85 to 150° C.; 85 to 145° C.; 85to 140° C.; 85 to 138° C.; 85 to 135° C.; 85 to 130° C.; 85 to 125° C.;85 to 120° C.; 85 to 115° C.; 85 to 110° C.; 85 to 105° C.; 85 to 100°C.; 85 to 95° C.; 85 to 90° C.; 90 to 300° C.; 90 to 190° C.; 90 to 180°C.; 90 to 170° C.; 90 to 160° C.; 90 to 155° C.; 90 to 150° C.; 90 to145° C.; 90 to 140° C.; 90 to 138° C.; 90 to 135° C.; 90 to 130° C.; 90to 125° C.; 90 to 120° C.; 90 to 115° C.; 90 to 110° C.; 90 to 105° C.;90 to 100° C.; 90 to 95° C.; 95 to 200° C.; 95 to 190° C.; 95 to 180°C.; 95 to 170° C.; 95 to 160° C.; 95 to 155° C.; 95 to 150° C.; 95 to145° C.; 95 to 140° C.; 95 to 138° C.; 95 to 135° C.; 95 to 130° C.; 95to 125° C.; 95 to 120° C.; 95 to 115° C.; 95 to 110° C.; 95 to 105° C.;95 to 100° C.; 100 to 300° C.; 100 to 190° C.; 100 to 180° C.; 100 to170° C.; 100 to 160° C.; 100 to 155° C.; 100 to 150° C.; 100 to 145° C.;100 to 140° C.; 100 to 138° C.; 100 to 135° C.; 100 to 130° C.; 100 to125° C.; 100 to 120° C.; 100 to 115° C.; 100 to 110° C.; 105 to 200° C.;105 to 190° C.; 105 to 180° C.; 105 to 170° C.; 105 to 160° C.; 105 to155° C.; 105 to 150° C.; 105 to 145° C.; 105 to 140° C.; 105 to 138° C.;105 to 135° C.; 105 to 130° C.; 105 to 125° C.; 105 to 120° C.; 105 to115° C.; 105 to 110° C.; 110 to 300° C.; 110 to 190° C.; 110 to 180° C.;110 to 170° C.; 110 to 160° C.; 110 to 155° C.; 110 to 150° C.; 110 to145° C.; 110 to 140° C.; 110 to 138° C.; 110 to 135° C.; 110 to 130° C.;110 to 125° C.; 110 to 120° C.; 110 to 115° C.; 115 to 200° C.; 115 to190° C.; 115 to 180° C.; 115 to 170° C.; 115 to 160° C.; 115 to 155° C.;115 to 150° C.; 115 to 145° C.; 115 to 140° C.; 115 to 138° C.; 115 to135° C.; 110 to 130° C.; 115 to 125° C.; 115 to 120° C.; 120 to 300° C.;120 to 190° C.; 120 to 180° C.; 120 to 170° C.; 120 to 160° C.; 120 to155° C.; 120 to 150° C.; 120 to 145° C.; 120 to 140° C.; 120 to 138° C.;120 to 135° C.; 120 to 130° C.; 125 to 200° C.; 125 to 190° C.; 125 to180° C.; 125 to 170° C.; 125 to 160° C.; 125 to 155° C.; 125 to 150° C.;125 to 145° C.; 125 to 140° C.; 125 to 138° C.; 125 to 135° C.; 127 to200° C.; 127 to 190° C.; 127 to 180° C.; 127 to 170° C.; 127 to 160° C.;127 to 150° C.; 127 to 145° C.; 127 to 140° C.; 127 to 138° C.; 127 to135° C.; 130 to 300° C.; 130 to 190° C.; 130 to 180° C.; 130 to 170° C.;130 to 160° C.; 130 to 155° C.; 130 to 150° C.; 130 to 145° C.; 130 to140° C.; 130 to 138° C.; 130 to 135° C.; 135 to 200° C.; 135 to 190° C.;135 to 180° C.; 135 to 170° C.; 135 to 160° C.; 135 to 155° C.; 135 to150° C.; 135 to 145° C.; 135 to 140° C.; 140 to 300° C.; 140 to 190° C.;140 to 180° C.; 140 to 170° C.; 140 to 160° C.; 140 to 155° C.; 140 to150° C.; 140 to 145° C.; 148 to 200° C.; 148 to 190° C.; 148 to 180° C.;148 to 170° C.; 148 to 160° C.; 148 to 155° C.; 148 to 150° C.; 150 to300° C.; 150 to 190° C.; 150 to 180° C.; 150 to 170° C.; 150 to 160; 155to 190° C.; 155 to 180° C.; 155 to 170° C.; and 155 to 165° C.

In other aspects of the invention, the glycol component for thepolyesters useful in the medical devices of the invention include butare not limited to at least one of the following combinations of ranges:1 to 99 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol and 1 to 99 mole% 1,4-cyclohexanedimethanol; 1 to 95 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 5 to 99 mole %1,4-cyclohexanedimethanol; 1 to 90 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 10 to 99 mole %1,4-cyclohexanedimethanol; 1 to 85 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 15 to 99 mole %1,4-cyclohexanedimethanol; 1 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 99 mole %1,4-cyclohexanedimethanol, 1 to 75 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 99 mole %1,4-cyclohexanedimethanol; 1 to 70 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 99 mole %1,4-cyclohexanedimethanol; 1 to 65 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 99 mole %1,4-cyclohexanedimethanol; 1 to 60 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 99 mole %1,4-cyclohexanedimethanol; 1 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 99 mole %1,4-cyclohexanedimethanol; 1 to 50 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 50 to 99 mole %1,4-cyclohexanedimethanol; 1 to 45 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 99 mole %1,4-cyclohexanedimethanol; 1 to 40 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 99 mole %1,4-cyclohexanedimethanol; 1 to 35 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 99 mole %1,4-cyclohexanedimethanol; 1 to 30 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 99 mole %1,4-cyclohexanedimethanol; 1 to 25 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 75 to 99 mole %1,4-cyclohexanedimethanol; 1 to 20 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 80 to 99 mole %1,4-cyclohexanedimethanol; 1 to 15 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 85 to 99 mole %1,4-cyclohexanedimethanol; 1 to 10 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 90 to 99 mole %1,4-cyclohexanedimethanol; and 1 to 5 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 95 to 99 mole %1,4-cyclohexanedimethanol.

In other aspects of the invention, the glycol component for thepolyesters useful in the medical devices of the invention include butare not limited to at least one of the following combinations of ranges:5 to less than 50 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol andgreater than 50 to 95 mole % 1,4-cyclohexanedimethanol; 5 to 45 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 95 mole %1,4-cyclohexanedimethanol; 5 to 40 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 95 mole %1,4-cyclohexanedimethanol; 5 to 35 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 95 mole %1,4-cyclohexanedimethanol; 5 to less than 35 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 65 to 95 mole %1,4-cyclohexanedimethanol; 5 to 30 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 95 mole %1,4-cyclohexanedimethanol; 5 to 25 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 75 to 95 mole %1,4-cyclohexanedimethanol; 10 to less than 50 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 50 to 90 mole %1,4-cyclohexanedimethanol; 10 to 45 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 90 mole %1,4-cyclohexanedimethanol; 10 to 40 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 90 mole %1,4-cyclohexanedimethanol; 10 to 35 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 90 mole % 1,4-cyclohexanedimethanol; 10 to less than 35 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 65 up to 90mole % 1,4-cyclohexanedimethanol; 10 to 30 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 90 mole %1,4-cyclohexanedimethanol; 10 to 25 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 75 to 90 mole %1,4-cyclohexanedimethanol; 15 to less than 50 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 50 up to 85mole % 1,4-cyclohexanedimethanol; 15 to 45 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 85 mole %1,4-cyclohexanedimethanol; 15 to 40 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 85 mole %1,4-cyclohexanedimethanol; 15 to 35 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 85 mole %1,4-cyclohexanedimethanol; 15 to 30 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 85 mole %1,4-cyclohexanedimethanol; 15 to 25 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 75 to 85 mole %1,4-cyclohexanedimethanol; and 17 to 23 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 77 to 83 mole %1,4-cyclohexanedimethanol.

In other aspects of the invention, the glycol component for thepolyesters useful in the medical devices of the invention include butare not limited to at least one of the following combinations of ranges:20 to 99 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol and 1 to 80 mole% 1,4-cyclohexanedimethanol; 20 to 95 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 5 to 80 mole %1,4-cyclohexanedimethanol; 20 to 90 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 10 to 80 mole %1,4-cyclohexanedimethanol; 20 to 85 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 15 to 80 mole %1,4-cyclohexanedimethanol; 20 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 80 mole %1,4-cyclohexanedimethanol, 20 to 75 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 80 mole %1,4-cyclohexanedimethanol; 20 to 70 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 80 mole %1,4-cyclohexanedimethanol; 20 to 65 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 80 mole %1,4-cyclohexanedimethanol; 20 to 60 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 80 mole %1,4-cyclohexanedimethanol; 20 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 80 mole %1,4-cyclohexanedimethanol; 20 to 50 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 50 to 80 mole %1,4-cyclohexanedimethanol; 20 to 45 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 80 mole %1,4-cyclohexanedimethanol; 20 to 40 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 80 mole %1,4-cyclohexanedimethanol; 20 to 35 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 80 mole %1,4-cyclohexanedimethanol; 20 to 30 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 80 mole %1,4-cyclohexanedimethanol; and 20 to 25 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 75 to 80 mole %1,4-cyclohexanedimethanol.

In other aspects of the invention, the glycol component for thepolyesters useful in the medical devices of the invention include butare not limited to at least one of the following combinations of ranges:25 to 99 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol and 1 to 75 mole% 1,4-cyclohexanedimethanol; 25 to 90 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 10 to 75 mole %1,4-cyclohexanedimethanol; 25 to 85 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 15 to 75 mole %1,4-cyclohexanedimethanol; 25 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 75 mole %1,4-cyclohexanedimethanol, 25 to 75 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 75 mole %1,4-cyclohexanedimethanol; 25 to 70 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 75 mole %1,4-cyclohexanedimethanol; 25 to 65 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 75 mole %1,4-cyclohexanedimethanol; 25 to 60 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 75 mole %1,4-cyclohexanedimethanol; 25 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 75 mole %1,4-cyclohexanedimethanol; 25 to 50 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 50 to 75 mole %1,4-cyclohexanedimethanol; 25 to 45 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 55 to 75 mole %1,4-cyclohexanedimethanol; 25 to 40 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 60 to 75 mole %1,4-cyclohexanedimethanol; 25 to 35 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 65 to 75 mole %1,4-cyclohexanedimethanol; 25 to 30 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 70 to 75 mole %1,4-cyclohexanedimethanol; and 25 to 25 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 75 to 75 mole %1,4-cyclohexanedimethanol.

In other aspects of the invention, the glycol component for thepolyesters useful in the medical devices of the invention include butare not limited to at least one of the following combinations of ranges:35 to 80 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 65mole % 1,4-cyclohexanedimethanol; 37 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 63 mole %1,4-cyclohexanedimethanol; 40 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 60 mole %1,4-cyclohexanedimethanol; 45 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 55 mole %1,4-cyclohexanedimethanol; 50 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 50 mole %1,4-cyclohexanedimethanol; greater than 50 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to less than 50 mole %1,4-cyclohexanedimethanol; 55 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 45 mole %1,4-cyclohexanedimethanol; 60 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 40 mole %1,4-cyclohexanedimethanol; 65 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 35 mole %1,4-cyclohexanedimethanol; 70 to 80 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to 30 mole % 1,4-cyclohexanedimethanol; 40 to 75mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 60 mole %1,4-cyclohexanedimethanol; 45 to 75 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 55 mole %1,4-cyclohexanedimethanol; 50 to 75 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 50 mole %1,4-cyclohexanedimethanol; 55 to 75 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 45 mole %1,4-cyclohexanedimethanol; 60 to 75 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 40 mole %1,4-cyclohexanedimethanol; 65 to 75 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to 35 mole %1,4-cyclohexanedimethanol; 40 to 70 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 60 mole %1,4-cyclohexanedimethanol; 45 to 70 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 55 mole %1,4-cyclohexanedimethanol; 50 to 70 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 50 mole %1,4-cyclohexanedimethanol; greater than 50 to 99 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 1 to less than 55 mole %1,4-cyclohexanedimethanol; greater than 50 to 80 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 20 to less than 50 mole %1,4-cyclohexanedimethanol; greater than 50 to 75 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 25 to less than 50 mole %1,4-cyclohexanedimethanol; greater than 50 to 70 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to less than 50 mole %1,4-cyclohexanedimethanol; 55 to 70 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 45 mole %1,4-cyclohexanedimethanol; 60 to 70 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 40 mole %1,4-cyclohexanedimethanol; 40 to 65 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 60 mole %1,4-cyclohexanedimethanol; 40 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 60 mole %1,4-cyclohexanedimethanol; 40 to less than 45 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and greater than 55 to 60 mole %1,4-cyclohexanedimethanol; 45 to 65 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 55 mole % 1,4-cyclohexanedimethanol; greaterthan 50 to 65 mole % 2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 toless than 50 mole % 1,4-cyclohexanedimethanol; 50 to 65 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 50 mole %1,4-cyclohexanedimethanol; 55 to 65 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 45 mole %1,4-cyclohexanedimethanol; 40 to 60 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 60 mole %1,4-cyclohexanedimethanol; 45 to 60 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 55 mole %1,4-cyclohexanedimethanol; 45 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 55 mole %1,4-cyclohexanedimethanol; greater than 45 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol; 45 to less than 55 mole %1,4-cyclohexanedimethanol; and 46 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 54 mole %1,4-cyclohexanedimethanol; and 46 to 65 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35 to 54 mole %1,4-cyclohexanedimethanol.

In addition to the diols set forth above, the polyesters useful in thepolyester compositions of the medical devices of the invention may bemade from 1,3-propanediol, 1,4-butanediol, or mixtures thereof. It iscontemplated that compositions of the invention made from1,3-propanediol, 1,4-butanediol, or mixtures thereof can possess atleast one of the Tg ranges described herein, at least one of theinherent viscosity ranges described herein, and/or at least one of theglycol or diacid ranges described herein. In addition or in thealternative, the polyesters made from 1,3-propanediol or 1,4-butanediolor mixtures thereof may also be made from 1,4-cyclohexanedimethanol inat least one of the following amounts: from 0.1 to 99 mole %; from 0.1to 80 mole %; from 0.1 to 70 mole %; from 0.1 to 60 mole %; from 0.1 to50 mole %; from 0.1 to 40 mole %; from 0.1 to 35 mole %; from 0.1 to 30mole %; from 0.1 to 25 mole %; from 0.1 to 20 mole %; from 0.1 to 15mole %; from 0.1 to 10 mole %; from 0.1 to 5 mole %; from 1 to 99 mole%; from 1 to 80 mole %; from 1 to 70 mole %; from 1 to 60 mole %; from 1to 50 mole %; from 1 to 40 mole %; from 1 to 35 mole %; from 1 to 30mole %; from 1 to 25 mole %; from 1 to 20 mole %; from 1 to 15 mole %;from 1 to 10 mole %; from 1 to 5 mole %; from 5 to 80 mole %; 5 to 70mole %; from 5 to 60 mole %; from 5 to 50 mole %; from 5 to 40 mole %;from 5 to 35 mole %; from 5 to 30 mole %; from 5 to 25 mole %; from 5 to20 mole %; and from 5 to 15 mole %; from 5 to 10 mole %; from 10 to 99mole %; from 10 to 80 mole %; from 10 to 70 mole %; from 10 to 60 mole%; from 10 to 50 mole %; from 10 to 40 mole %; from 10 to 35 mole %;from 10 to 30 mole %; from 10 to 25 mole %; from 10 to 20 mole %; from10 to 15 mole %; from 20 to 99 mole %; from 20 to 80 mole %; from 20 to70 mole %; from 20 to 60 mole %; from 20 to 50 mole %; from 20 to 40mole %; from 20 to 35 mole %; from 20 to 30 mole %; and from 20 to 25mole %.

For embodiments of the invention, the polyesters useful in the inventionmay exhibit at least one of the following inherent viscosities asdetermined in 60/40 (wt/wt) phenol/tetrachloroethane at a concentrationof 0.5 g/100 ml at 25° C.: 0.10 to 1.2 dL/g; 0.10 to 1.1 dL/g; 0.10 to 1dL/g; 0.10 to less than 1 dL/g; 0.10 to 0.98 dL/g; 0.10 to 0.95 dL/g;0.10 to 0.90 dL/g; 0.10 to 0.85 dL/g; 0.10 to 0.80 dL/g; 0.10 to 0.75dL/g; 0.10 to less than 0.75 dL/g; 0.10 to 0.72 dL/g; 0.10 to 0.70 dL/g;0.10 to less than 0.70 dL/g; 0.10 to 0.68 dL/g; 0.10 to less than 0.68dL/g; 0.10 to 0.65 dL/g; 0.20 to 1.2 dL/g; 0.20 to 1.1 dL/g; 0.20 to 1dL/g; 0.20 to less than 1 dL/g; 0.20 to 0.98 dL/g; 0.20 to 0.95 dL/g;0.20 to 0.90 dL/g; 0.20 to 0.85 dL/g; 0.20 to 0.80 dL/g; 0.20 to 0.75dL/g; 0.20 to less than 0.75 dL/g; 0.20 to 0.72 dL/g; 0.20 to 0.70 dL/g;0.20 to less than 0.70 dL/g; 0.20 to 0.68 dL/g; 0.20 to less than 0.68dL/g; 0.20 to 0.65 dL/g; 0.35 to 1.2 dL/g; 0.35 to 1.1 dL/g; 0.35 to 1dL/g; 0.35 to less than 1 dL/g; 0.35 to 0.98 dL/g; 0.35 to 0.95 dL/g;0.35 to 0.90 dL/g; 0.35 to 0.85 dL/g; 0.35 to 0.80 dL/g; 0.35 to 0.75dL/g; 0.35 to less than 0.75 dL/g; 0.35 to 0.72 dL/g; 0.35 to 0.70 dL/g;0.35 to less than 0.70 dL/g; 0.35 to 0.68 dL/g; 0.35 to less than 0.68dL/g; 0.35 to 0.65 dL/g; 0.40 to 1.2 dL/g; 0.40 to 1.1 dL/g; 0.40 to 1dL/g; 0.40 to less than 1 dL/g; 0.40 to 0.98 dL/g; 0.40 to 0.95 dL/g;0.40 to 0.90 dL/g; 0.40 to 0.85 dL/g; 0.40 to 0.80 dL/g; 0.40 to 0.75dL/g; 0.40 to less than 0.75 dL/g; 0.40 to 0.72 dL/g; 0.40 to 0.70 dL/g;0.40 to less than 0.70 dL/g; 0.40 to 0.68 dL/g; 0.40 to less than 0.68dL/g; 0.40 to 0.65 dL/g; greater than 0.42 to 1.2 dL/g; greater than0.42 to 1.1 dL/g; greater than 0.42 to 1 dL/g; greater than 0.42 to lessthan 1 dL/g; greater than 0.42 to 0.98 dL/g; greater than 0.42 to 0.95dL/g; greater than 0.42 to 0.90 dL/g; greater than 0.42 to 0.85 dL/g;greater than 0.42 to 0.80 dL/g; greater than 0.42 to 0.75 dL/g; greaterthan 0.42 to less than 0.75 dL/g; greater than 0.42 to 0.72 dL/g;greater than 0.42 to less than 0.70 dL/g; greater than 0.42 to 0.68dL/g; greater than 0.42 to less than 0.68 dL/g; and greater than 0.42 to0.65 dL/g.

For embodiments of the invention, the polyesters useful in the inventionmay exhibit at least one of the following inherent viscosities asdetermined in 60/40 (wt/wt) phenol/tetrachloroethane at a concentrationof 0.5 g/100 ml at 25° C.: 0.45 to 1.2 dL/g; 0.45 to 1.1 dL/g; 0.45 to 1dL/g; 0.45 to 0.98 dL/g; 0.45 to 0.95 dL/g; 0.45 to 0.90 dL/g; 0.45 to0.85 dL/g; 0.45 to 0.80 dL/g; 0.45 to 0.75 dL/g; 0.45 to less than 0.75dL/g; 0.45 to 0.72 dL/g; 0.45 to 0.70 dL/g; 0.45 to less than 0.70 dL/g;0.45 to 0.68 dL/g; 0.45 to less than 0.68 dL/g; 0.45 to 0.65 dL/g; 0.50to 1.2 dL/g; 0.50 to 1.1 dL/g; 0.50 to 1 dL/g; 0.50 to less than 1 dL/g;0.50 to 0.98 dL/g; 0.50 to 0.95 dL/g; 0.50 to 0.90 dL/g; 0.50 to 0.85dL/g; 0.50 to 0.80 dL/g; 0.50 to 0.75 dL/g; 0.50 to less than 0.75 dL/g;0.50 to 0.72 dL/g; 0.50 to 0.70 dL/g; 0.50 to less than 0.70 dL/g; 0.50to 0.68 dL/g; 0.50 to less than 0.68 dL/g; 0.50 to 0.65 dL/g; 0.55 to1.2 dL/g; 0.55 to 1.1 dL/g; 0.55 to 1 dL/g; 0.55 to less than 1 dL/g;0.55 to 0.98 dL/g; 0.55 to 0.95 dL/g; 0.55 to 0.90 dL/g; 0.55 to 0.85dL/g; 0.55 to 0.80 dL/g; 0.55 to 0.75 dL/g; 0.55 to less than 0.75 dL/g;0.55 to 0.72 dL/g; 0.55 to 0.70 dL/g; 0.55 to less than 0.70 dL/g; 0.55to 0.68 dL/g; 0.55 to less than 0.68 dL/g; 0.55 to 0.65 dL/g; 0.58 to1.2 dL/g; 0.58 to 1.1 dL/g; 0.58 to 1 dL/g; 0.58 to less than 1 dL/g;0.58 to 0.98 dL/g; 0.58 to 0.95 dL/g; 0.58 to 0.90 dL/g; 0.58 to 0.85dL/g; 0.58 to 0.80 dL/g; 0.58 to 0.75 dL/g; 0.58 to less than 0.75 dL/g;0.58 to 0.72 dL/g; 0.58 to 0.70 dL/g; 0.58 to less than 0.70 dL/g; 0.58to 0.68 dL/g; 0.58 to less than 0.68 dL/g; 0.58 to 0.65 dL/g; 0.60 to1.2 dL/g; 0.60 to 1.1 dL/g; 0.60 to 1 dL/g; 0.60 to less than 1 dL/g;0.60 to 0.98 dL/g; 0.60 to 0.95 dL/g; 0.60 to 0.90 dL/g; 0.60 to 0.85dL/g; 0.60 to 0.80 dL/g; 0.60 to 0.75 dL/g; 0.60 to less than 0.75 dL/g;0.60 to 0.72 dL/g; 0.60 to 0.70 dL/g; 0.60 to less than 0.70 dL/g; 0.60to 0.68 dL/g; 0.60 to less than 0.68 dL/g; 0.60 to 0.65 dL/g; 0.65 to1.2 dL/g; 0.65 to 1.1 dL/g; 0.65 to 1 dL/g; 0.65 to less than 1 dL/g;0.65 to 0.98 dL/g; 0.65 to 0.95 dL/g; 0.65 to 0.90 dL/g; 0.65 to 0.85dL/g; 0.65 to 0.80 dL/g; 0.65 to 0.75 dL/g; 0.65 to less than 0.75 dL/g;0.65 to 0.72 dL/g; 0.65 to 0.70 dL/g; 0.65 to less than 0.70 dL/g; 0.68to 1.2 dL/g; 0.68 to 1.1 dL/g; 0.68 to 1 dL/g; 0.68 to less than 1 dL/g;0.68 to 0.98 dL/g; 0.68 to 0.95 dL/g; 0.68 to 0.90 dL/g; 0.68 to 0.85dL/g; 0.68 to 0.80 dL/g; 0.68 to 0.75 dL/g; 0.68 to less than 0.75 dL/g;0.68 to 0.72 dL/g; greater than 0.76 dL/g to 1.2 dL/g; greater than 0.76dL/g to 1.1 dL/g; greater than 0.76 dL/g to 1 dL/g; greater than 0.76dL/g to less than 1 dL/g; greater than 0.76 dL/g to 0.98 dL/g; greaterthan 0.76 dL/g to 0.95 dL/g; greater than 0.76 dL/g to 0.90 dL/g;greater than 0.80 dL/g to 1.2 dL/g; greater than 0.80 dL/g to 1.1 dL/g;greater than 0.80 dL/g to 1 dL/g; greater than 0.80 dL/g to less than 1dL/g; greater than 0.80 dL/g to 1.2 dL/g; greater than 0.80 dL/g to 0.98dL/g; greater than 0.80 dL/g to 0.95 dL/g; greater than 0.80 dL/g to0.90 dL/g.

It is contemplated that compositions useful in the medical device(s) ofthe invention can possess at least one of the inherent viscosity rangesdescribed herein and at least one of the monomer ranges for thecompositions described herein unless otherwise stated. It is alsocontemplated that compositions useful in the medical device(s) of theinvention can possess at least one of the Tg ranges described herein andat least one of the monomer ranges for the compositions described hereinunless otherwise stated. It is also contemplated that compositionsuseful in the medical device(s) of the invention can posses at least oneof the inherent viscosity ranges described herein, at least one of theTg ranges described herein, and at least one of the monomer ranges forthe compositions described herein unless otherwise stated.

For the desired polyester, the molar ratio of cis/trans2,2,4,4-tetramethyl-1,3-cyclobutanediol can vary from the pure form ofeach or mixtures thereof. In certain embodiments, the molar percentagesfor cis and/or trans 2,2,4,4-tetramethyl-1,3-cyclobutanediol are greaterthan 50 mole % cis and less than 50 mole % trans; or greater than 55mole % cis and less than 45 mole % trans; or 30 to 70 mole % cis and 70to 30% trans; or 40 to 60 mole % cis and 60 to 40 mole % trans; or 50 to70 mole % trans and 50 to 30% cis or 50 to 70 mole % cis and 50 to 30%trans; or 60 to 70 mole % cis and 30 to 40 mole % trans; or greater than70 mole % cis and less than 30 mole % trans; wherein the total sum ofthe mole percentages for cis- andtrans-2,2,4,4-tetramethyl-1,3-cyclobutanediol is equal to 100 mole %.The molar ratio of cis/trans 1,4-cyclohexanedimethanol can vary withinthe range of 50/50 to 0/100, for example, between 40/60 to 20/80.

In certain embodiments, terephthalic acid, an ester thereof, such as,for example, dimethyl terephthalate, or a mixture of terephthalic acidand an ester thereof, makes up most or all of the dicarboxylic acidcomponent used to form the polyesters useful in the invention. Incertain embodiments, terephthalic acid residues can make up a portion orall of the dicarboxylic acid component used to form the presentpolyester at a concentration of at least 70 mole %, such as at least 80mole %, at least 90 mole %, at least 95 mole %, at least 99 mole %, or amole % of 100. In certain embodiments, higher amounts of terephthalicacid can be used in order to produce a higher impact strength polyester.For the purposes of this disclosure, the terms “terephthalic acid” and“dimethyl terephthalate” are used interchangeably herein. In oneembodiment, dimethyl terephthalate is part or all of the dicarboxylicacid component used to make the polyesters useful in the presentinvention. In all embodiments, ranges of from 70 to 100 mole %; or 80 to100 mole %; or 90 to 100 mole %; or 99 to 100 mole %; or 100 mole %terephthalic acid and/or dimethyl terephthalate and/or mixtures thereofmay be used.

In addition to terephthalic acid residues, the dicarboxylic acidcomponent of the polyesters useful in the medical devices and methods ofthe present invention can comprise up to 30 mole %, up to 20 mole %, upto 10 mole %, up to 5 mole %, or up to 1 mole % modifying aromaticdicarboxylic acids. Yet another embodiment contains 0 mole % modifyingaromatic dicarboxylic acids. Thus, if present, it is contemplated thatthe amount of one or more modifying aromatic dicarboxylic acids canrange from any of these preceding endpoint values including, forexample, from 0.01 to 30 mole %, 0.01 to 20 mole %, from 0.01 to 10 mole%, from 0.01 to 5 mole % and from 0.01 to 1 mole. In one embodiment,modifying aromatic dicarboxylic acids that may be used in the presentinvention include but are not limited to those having up to 20 carbonatoms, and which can be linear, para-oriented, or symmetrical. Examplesof modifying aromatic dicarboxylic acids which may be used in thisinvention include, but are not limited to, isophthalic acid,4,4′-biphenyldicarboxylic acid, 1,4-, 1,5-, 2,6-,2,7-naphthalenedicarboxylic acid, and trans-4,4′-stilbenedicarboxylicacid, and esters thereof. In one embodiment, the modifying aromaticdicarboxylic acid is isophthalic acid.

In addition to terephthalic acid residues, the dicarboxylic acidcomponent of the polyesters useful in the invention can comprise up to30 mole %, up to 20 mole %, up to 10 mole %, up to 5 mole %, or up to 1mole % modifying aromatic dicarboxylic acids. Yet another embodimentcontains 0 mole % modifying aromatic dicarboxylic acids. Thus, ifpresent, it is contemplated that the amount of one or more modifyingaromatic dicarboxylic acids can range from any of these precedingendpoint values including, for example, from 0.01 to 30 mole %, 0.01 to20 mole %, from 0.01 to 10 mole %, from 0.01 to 5 mole % and from 0.01to 1 mole. In one embodiment, modifying aromatic dicarboxylic acids thatmay be used in the present invention include but are not limited tothose having up to 20 carbon atoms, and which can be linear,para-oriented, or symmetrical. Examples of modifying aromaticdicarboxylic acids which may be used in this invention include, but arenot limited to, isophthalic acid, 4,4′-biphenyldicarboxylic acid, 1,4-,1,5-, 2,6-, 2,7-naphthalenedicarboxylic acid, andtrans-4,4′-stilbenedicarboxylic acid, and esters thereof. In oneembodiment, the modifying aromatic dicarboxylic acid is isophthalicacid.

The carboxylic acid component of the polyesters useful in the medicaldevices of the invention can be further modified with up to 10 mole %,up to 5 mole % or up to 1 mole % of one or more aliphatic dicarboxylicacids containing 2-16 carbon atoms, such as, for example, malonic,succinic, glutaric, adipic, pimelic, suberic, azelaic and dodecanedioicdicarboxylic acids. Certain embodiments can also comprise 0.01 or moremole %, 0.1 or more mole %, 1 or more mole %, 5 or more mole %, or 10 ormore mole % of one or more modifying aliphatic dicarboxylic acids. Yetanother embodiment contains 0 mole % modifying aliphatic dicarboxylicacids. Thus, if present, it is contemplated that the amount of one ormore modifying aliphatic dicarboxylic acids can range from any of thesepreceding endpoint values including, for example, from 0.01 to 10 mole %and from 0.1 to 10 mole %. The total mole % of the dicarboxylic acidcomponent is 100 mole %.

Esters of terephthalic acid and the other modifying dicarboxylic acidsor their corresponding esters and/or salts may be used instead of thedicarboxylic acids. Suitable examples of dicarboxylic acid estersinclude, but are not limited to, the dimethyl, diethyl, dipropyl,diisopropyl, dibutyl, and diphenyl esters. In one embodiment, the estersare chosen from at least one of the following: methyl, ethyl, propyl,isopropyl, and phenyl esters.

The 1,4-cyclohexanedimethanol may be cis, trans, or a mixture thereof,such as a cis/trans ratio of 60:40 to 40:60. In another embodiment, thetrans-1,4-cyclohexanedimethanol can be present in an amount of 60 to 80mole %.

The glycol component of the polyester portion of the polyestercomposition useful in the invention can contain 25 mole % or less of oneor more modifying glycols which are not2,2,4,4-tetramethyl-1,3-cyclobutanediol or 1,4-cyclohexanedimethanol; inone embodiment, the polyester useful in the invention may contain lessthan 15 mole % of one or more modifying glycols. In another embodiment,the polyesters useful in the invention can contain 10 mole % or less ofone or more modifying glycols. In another embodiment, the polyestersuseful in the invention can contain 5 mole % or less of one or moremodifying glycols. In another embodiment, the polyesters useful in theinvention can contain 3 mole % or less of one or more modifying glycols.In another embodiment, the polyesters useful in the invention cancontain 0 mole % of one or more modifying glycols. Certain embodimentscan also contain 0.01 or more mole %, such as 0.1 or more mole %, 1 ormore mole %, 5 or more mole %, or 10 or more mole % of one or moremodifying glycols. Thus, if present, it is contemplated that the amountof one or more modifying glycols can range from any of these precedingendpoint values including, for example, from 0.01 to 15 mole % and from0.1 to 10 mole %.

Modifying glycols useful in the polyester useful in the invention referto diols other than 2,2,4,4-tetramethyl-1,3-cyclobutanediol and1,4-cyclohexanedimethanol and may contain 2 to 16 carbon atoms. Examplesof suitable modifying glycols include, but are not limited to, ethyleneglycol residues, 1,2-propanediol, 1,3-propanediol, neopentyl glycol,1,4-butanediol, 1,5-pentanediol, 1,6-hexanediol, p-xylene glycol ormixtures thereof. In one embodiment, the modifying glycol is ethyleneglycol residues. In another embodiment, the modifying glycols are1,3-propanediol and/or 1,4-butanediol. In another embodiment, ethyleneglycol residues are excluded as a modifying diol. In another embodiment,1,3-propanediol and 1,4-butanediol are excluded as modifying diols. Inanother embodiment, 2,2-dimethyl-1,3-propanediol is excluded as amodifying diol.

The polyesters and/or the polycarbonates useful in the invention cancomprise from 0 to 10 weight percent (wt %), for example, from 0.01 to 5weight percent, from 0.01 to 1 weight percent, from 0.05 to 5 weightpercent, from 0.05 to 1 weight percent, or from 0.1 to 0.7 weightpercent, based on the total weight of the polyester and/orpolycarbonate, respectively, of one or more residues of a branchingmonomer, also referred to herein as a branching agent, having 3 or morecarboxyl substituents, hydroxyl substituents, or a combination thereof.In certain embodiments, the branching monomer or agent may be addedprior to and/or during and/or after the polymerization of the polyester.The polyester(s) useful in the invention can thus be linear or branched.The polycarbonate can also be linear or branched. In certainembodiments, the branching monomer or agent may be added prior to and/orduring and/or after the polymerization of the polycarbonate.

Examples of branching monomers include, but are not limited to,multifunctional acids or multifunctional alcohols such as trimelliticacid, trimellitic anhydride, pyromellitic dianhydride,trimethylolpropane, glycerol, pentaerythritol, citric acid, tartaricacid, 3-hydroxyglutaric acid and the like. In one embodiment, thebranching monomer residues comprise 0.1 to 0.7 mole percent of one ormore residues of: trimellitic anhydride, pyromellitic dianhydride,glycerol, sorbitol, 1,2,6-hexanetriol, pentaerythritol,trimethylolethane, or trimesic acid. The branching monomer may be addedto the polyester reaction mixture or blended with the polyester in theform of a concentrate as described, for example, in U.S. Pat. Nos.5,654,347 and 5,696,176, the disclosure regarding branching monomerswhich is incorporated herein by reference.

The carboxylic acid component of the polyesters useful in the medicaldevices and methods of the present invention can be further modifiedwith up to 10 mole %, up to 5 mole % or up to 1 mole % of one or morealiphatic dicarboxylic acids containing 2-16 carbon atoms, such as, forexample, malonic, succinic, glutaric, adipic, pimelic, suberic, azelaicand dodecanedioic dicarboxylic acids. Certain embodiments can alsocomprise 0.01 or more mole %, 0.1 or more mole %, 1 or more mole %, 5 ormore mole %, or 10 or more mole % of one or more modifying aliphaticdicarboxylic acids. Yet another embodiment contains 0 mole % modifyingaliphatic dicarboxylic acids. Thus, if present, it is contemplated thatthe amount of one or more modifying aliphatic dicarboxylic acids canrange from any of these preceding endpoint values including, forexample, from 0.01 to 10 mole % and from 0.1 to 10 mole %. The totalmole % of the dicarboxylic acid component is 100 mole %.

Esters of terephthalic acid and the other modifying dicarboxylic acidsor their corresponding esters and/or salts may be used instead of thedicarboxylic acids. Suitable examples of dicarboxylic acid estersinclude, but are not limited to, the dimethyl, diethyl, dipropyl,diisopropyl, dibutyl, and diphenyl esters. In one embodiment, the estersare chosen from at least one of the following: methyl, ethyl, propyl,isopropyl, and phenyl esters.

The 1,4-cyclohexanedimethanol may be cis, trans, or a mixture thereof,such as a cis/trans ratio of 60:40 to 40:60. In another embodiment, thetrans-1,4-cyclohexanedimethanol can be present in an amount of 60 to 80mole %.

The glycol component of the polyester portion of the polyestercomposition useful in the invention can contain 25 mole % or less of oneor more modifying glycols which are not2,2,4,4-tetramethyl-1,3-cyclobutanediol or 1,4-cyclohexanedimethanol; inone embodiment, the polyester useful in the invention may contain lessthan 15 mole % or of one or more modifying glycols. In anotherembodiment, the polyesters useful in the invention can contain 10 mole %or less of one or more modifying glycols. In another embodiment, thepolyesters useful in the invention can contain 5 mole % or less of oneor more modifying glycols. In another embodiment, the polyesters usefulin the invention can contain 3 mole % or less of one or more modifyingglycols. In another embodiment, the polyesters useful in the inventioncan contain 0 mole % modifying glycols. Thus, if present, it iscontemplated that the amount of one or more modifying glycols can rangefrom any of these preceding endpoint values including, for example, from0.01 to 15 mole % and from 0.1 to 10 mole %.

Modifying glycols useful in polyesters useful in the invention refer todiols other than 2,2,4,4-tetramethyl-1,3-cyclobutanediol and1,4-cyclohexanedimethanol and can contain 2 to 16 carbon atoms. Examplesof suitable modifying glycols include, but are not limited to, ethyleneglycol, diethylene glycol, 1,2-propanediol, 1,3-propanediol, neopentylglycol, 1,4-butanediol, 1,5-pentanediol, 1,6-hexanediol, p-xyleneglycol, or mixtures thereof. One embodiment for the modifying glycol isethylene glycol. Other modifying glycols include, but are not limitedto, 1,3-propanediol and 1,4-butanediol. In another embodiment, ethyleneglycol is excluded as a modifying diol. In another embodiment,1,3-propanediol and 1,4-butanediol are excluded as modifying diols. Inanother embodiment, 2,2-dimethyl-1,3-propanediol is excluded as amodifying diol.

The polyesters and/or the polycarbonates useful in the polyesterscompositions of the invention can comprise from 0 to 10 mole percent,for example, from 0.01 to 5 mole percent, from 0.01 to 1 mole percent,from 0.05 to 5 mole percent, from 0.05 to 1 mole percent, or from 0.1 to0.7 mole percent, or 0.1 to 0.5 mole percent, based the total molepercentages of either the diol or diacid residues; respectively, of oneor more residues of a branching monomer, also referred to herein as abranching agent, having 3 or more carboxyl substituents, hydroxylsubstituents, or a combination thereof. In certain embodiments, thebranching monomer or agent may be added prior to and/or during and/orafter the polymerization of the polyester. The polyester(s) useful inthe invention can thus be linear or branched. The polycarbonate can alsobe linear or branched. In certain embodiments, the branching monomer oragent may be added prior to and/or during and/or after thepolymerization of the polycarbonate.

Examples of branching monomers include, but are not limited to,multifunctional acids or multifunctional alcohols such as trimelliticacid, trimellitic anhydride, pyromellitic dianhydride,trimethylolpropane, glycerol, pentaerythritol, citric acid, tartaricacid, 3-hydroxyglutaric acid and the like. In one embodiment, thebranching monomer residues can comprise 0.1 to 0.7 mole percent of oneor more residues chosen from at least one of the following: trimelliticanhydride, pyromellitic dianhydride, glycerol, sorbitol,1,2,6-hexanetriol, pentaerythritol, trimethylolethane, and/or trimesicacid. The branching monomer may be added to the polyester reactionmixture or blended with the polyester in the form of a concentrate asdescribed, for example, in U.S. Pat. Nos. 5,654,347 and 5,696,176, whosedisclosure regarding branching monomers is incorporated herein byreference.

The glass transition temperature (Tg) of the polyesters useful in themedical devices and methods of the present invention was determinedusing a TA DSC 2920 from Thermal Analyst Instrument at a scan rate of20° C./min.

Because of the long crystallization half-times (e.g., greater than 5minutes) at 170° C. exhibited by certain polyesters useful in thepresent invention, it can be possible to produce articles, such asmedical devices, including, but not limited to, injection molded parts,injection blow molded articles, injection stretch blow molded articles,extruded film, extruded sheet, extrusion blow molded articles, extrusionstretch blow molded articles, and fibers. A thermoformable sheet is anexample of an article of manufacture provided by this invention. Thepolyesters of the invention can be amorphous or semicrystalline. In oneaspect, certain polyesters useful in the invention can have a relativelylow crystallinity. Certain polyesters useful in the invention can thushave a substantially amorphous morphology, meaning that the polyesterscomprise substantially unordered regions of polymer.

In one embodiment, an “amorphous” polyester can have a crystallizationhalf-time of greater than 5 minutes at 170° C.; or greater than 10minutes at 170° C.; or greater than 50 minutes at 170° C.; or greaterthan 100 minutes at 170° C. or greater than 100 minutes at 170° C. Inone embodiment, of the invention, the crystallization half-times can begreater than 1,000 minutes at 170° C. In another embodiment of theinvention, the crystallization half-times of the polyesters useful inthe invention can be greater than 10,000 minutes at 170° C. Thecrystallization half time of the polyester, as used herein, may bemeasured using methods well-known to persons of skill in the art. Forexample, the crystallization half time of the polyester, t_(1/2), can bedetermined by measuring the light transmission of a sample via a laserand photo detector as a function of time on a temperature controlled hotstage. This measurement can be done by exposing the polymers to atemperature, T_(max), and then cooling it to the desired temperature.The sample can then be held at the desired temperature by a hot stagewhile transmission measurements are made as a function of time.Initially, the sample can be visually clear with high lighttransmission, and becomes opaque as the sample crystallizes. Thecrystallization half-time is the time at which the light transmission ishalfway between the initial transmission and the final transmission.T_(max) is defined as the temperature required to melt the crystallinedomains of the sample (if crystalline domains are present). The samplecan be heated to Tmax to condition the sample prior to crystallizationhalf time measurement. The absolute Tmax temperature is different foreach composition. For example PCT can be heated to some temperaturegreater than 290° C. to melt the crystalline domains.

As shown in Table 1 and FIG. 1 of the Examples,2,2,4,4-tetramethyl-1,3-cyclobutanediol is more effective than othercomonomers such ethylene glycol and isophthalic acid at increasing thecrystallization half-time, i.e., the time required for a polymer toreach half of its maximum crystallinity. By decreasing thecrystallization rate of PCT, i.e. increasing the crystallizationhalf-time, amorphous articles based on modified, PCT may be fabricatedby methods known in the art such as extrusion, injection molding, andthe like. As shown in Table 1, these materials can exhibit higher glasstransition temperatures and lower densities than other modified PCTcopolyesters.

The polyesters can exhibit an improvement in toughness combined withprocessability for some of the embodiments of the invention. Forexample, lowering the inherent viscosity slightly of the polyestersuseful in the invention results in a more processable melt viscositywhile retaining good physical properties of the polyesters such astoughness and heat resistance.

Increasing the content of 1,4-cyclohexanedimethanol in a copolyesterbased on terephthalic acid, ethylene glycol, and1,4-cyclohexanedimethanol can improve toughness, which can be determinedby the brittle-to-ductile transition temperature in a notched Izodimpact strength test as measured by ASTM D256. This toughnessimprovement, by lowering of the brittle-to-ductile transitiontemperature with 1,4-cyclohexanedimethanol, is believed to occur due tothe flexibility and conformational behavior of 1,4-cyclohexanedimethanolin the copolyester. Incorporating2,2,4,4-tetramethyl-1,3-cyclobutanediol into PCT is believed to improvetoughness, by lowering the brittle-to-ductile transition temperature, asshown in Table 2 and FIG. 2 of the Examples.

In one embodiment, the melt viscosity of the polyester(s) useful in theinvention is less than 30,000 poise as measured a 1 radian/second on arotary melt rheometer at 290° C. In another embodiment, the meltviscosity of the polyester(s) useful in the invention is less than20,000 poise as measured a 1 radian/second on a rotary melt rheometer at290° C.

In one embodiment, the melt viscosity of the polyester(s) useful in theinvention is less than 15,000 poise as measured at 1 radian/second(rad/sec) on a rotary melt rheometer at 290° C. In one embodiment, themelt viscosity of the polyester(s) useful in the invention is less than10,000 poise as measured at 1 radian/second (rad/sec) on a rotary meltrheometer at 290° C. In another embodiment, the melt viscosity of thepolyester(s) useful in the invention is less than 6,000 poise asmeasured at 1 radian/second on a rotary melt rheometer at 290° C.Viscosity at rad/sec is related to processability. Typical polymers haveviscosities of less than 10,000 poise as measured at 1 radian/secondwhen measured at their processing temperature. Polyesters are typicallynot processed above 290° C. Polycarbonate is typically processed at 290°C. The viscosity at 1 rad/sec of a typical 12 melt flow ratepolycarbonate is 7000 poise at 290° C.

In one embodiment of the invention, the polyesters useful in theinvention exhibit superior notched Izod impact strength in thicksections. Notched Izod impact strength, as described in ASTM D256, is acommon method of measuring toughness. When tested by the Izod method,polymers can exhibit either a complete break failure mode, where thetest specimen breaks into two distinct parts, or a partial or no breakfailure mode, where the test specimen remains as one part. The completebreak failure mode is associated with low energy failure. The partialand no break failure modes are associated with high energy failure. Atypical thickness used to measure Izod toughness is ⅛″. At thisthickness, very few polymers are believed to exhibit a partial or nobreak failure mode, polycarbonate being one notable example. When thethickness of the test specimen is increased to ¼″, however, nocommercial amorphous materials exhibit a partial or no break failuremode. In one embodiment, compositions of the present example exhibit ano break failure mode when tested in Izod using a ¼″ thick specimen.

The present polyesters useful in this invention can possess one or moreof the following properties: In one embodiment, the polyesters useful inthe invention exhibit a notched Izod impact strength of at least 150 J/m(3 ft-lb/in) at 23° C. with a 10-mil notch in a 3.2 mm (⅛-inch) thickbar determined according to ASTM D256; in one embodiment, the polyestersuseful in the invention exhibit a notched Izod impact strength of atleast (400 J/m) 7.5 ft-lb/in at 23° C. with a 10-mil notch in a 3.2 mm(⅛-inch) thick bar determined according to ASTM D256; in one embodiment,the polyesters useful in the invention exhibit a notched Izod impactstrength of at least 1000 J/m (18 ft-lb/in) at 23° C. with a 10-milnotch in a 3.2 mm (⅛-inch) thick bar determined according to ASTM D256.In one embodiment, the polyesters useful in the invention exhibit anotched Izod impact strength of at least 150 J/m (3 ft-lb/in) at 23° C.with a 10-mil notch in a 6.4 mm (¼-inch) thick bar determined accordingto ASTM D256; in one embodiment, the polyesters useful in the inventionexhibit a notched Izod impact strength of at least (400 J/m) 7.5ft-lb/in at 23° C. with a 10-mil notch in a 6.4 mm (¼-inch) thick bardetermined according to ASTM D256; in one embodiment, the polyestersuseful in the invention exhibit a notched Izod impact strength of atleast 1000 J/m (18 ft-lb/in) at 23° C. with a 10-mil notch in a 6.4 mm(¼-inch) thick bar determined according to ASTM D256.

In another embodiment, certain polyesters useful in the invention canexhibit an increase in notched Izod impact strength when measured at 0°C. of at least 3% or at least 5% or at least 10% or at least 15% ascompared to the notched Izod impact strength when measured at −5° C.with a 10-mil notch in a ⅛-inch thick bar determined according to ASTMD256. In addition, certain other polyesters useful in the invention canalso exhibit a retention of notched Izod impact strength within plus orminus 5% when measured at 0° C. through 30° C. with a 10-mil notch in a⅛-inch thick bar determined according to ASTM D256.

In yet another embodiment, certain polyesters useful in the inventioncan exhibit a retention in notched Izod impact strength with a loss ofno more than 70% when measured at 23° C. with a 10-mil notch in a ¼-inchthick bar determined according to ASTM D256 as compared to notched Izodimpact strength for the same polyester when measured at the sametemperature with a 10-mil notch in a ⅛-inch thick bar determinedaccording to ASTM D256.

In one embodiment, the polyesters useful in the invention can exhibit aductile-to-brittle transition temperature of less than 0° C. based on a10-mil notch in a ⅛-inch thick bar as defined by ASTM D256.

In one embodiment, the polyesters useful in the invention can exhibit atleast one of the following densities as determined using a gradientdensity column at 23° C.: a density of less than 1.2 g/ml at 23° C.; adensity of less than 1.18 g/ml at 23° C.; a density of 0.8 to 1.3 g/mlat 23° C.; a density of 0.80 to 1.2 g/ml at 23° C.; a density of 0.80 toless than 1.2 g/ml at 23° C.; a density of 1.0 to 1.3 g/ml at 23° C.; adensity of 1.0 to 1.2 g/ml at 23° C.; a density of 1.0 to 1.1 g/ml at23° C.; a density of 1.13 to 1.3 g/ml at 23° C.; a density of 1.13 to1.2 g/ml at 23° C.

In one embodiment, the polyesters useful in this invention can bevisually clear. The term “visually clear” is defined herein as anappreciable absence of cloudiness, haziness, and/or muddiness, wheninspected visually. In another embodiment, when the polyesters areblended with polycarbonate, including, but not limited to, bisphenol Apolycarbonates, the blends can be visually clear.

In other embodiments of the invention, the polyesters useful in theinvention may have a yellowness index (ASTM D-1925) of less than 50 orless than 20.

In one embodiment, the polyesters useful in the invention and/or thepolyester compositions of the invention, with or without toners, canhave color values L*, a* and b* which were determined using a Hunter LabUltrascan Spectra Colorimeter manufactured by Hunter Associates LabInc., Reston, Va. The color determinations are averages of valuesmeasured on either pellets of the polyesters or plaques or other itemsinjection molded or extruded from them. They are determined by theL*a*b* color system of the CIE (International Commission onIllumination) (translated), wherein L* represents the lightnesscoordinate, a* represents the red/green coordinate, and b* representsthe yellow/blue coordinate. In certain embodiments, the b* values forthe polyesters useful in the invention can be from −10 to less than 10and the L* values can be from 50 to 90. In other embodiments, the b*values for the polyesters useful in the invention can be present in oneof the following ranges: from:from −10 to 9; −10 to 8; −10 to 7; −10 to6; −10 to 5; −10 to 4; −10 to 3; −10 to 2; from −5 to 9; −5 to 8; −5 to7; −5 to 6; −5 to 5; −5 to 4; −5 to 3; −5 to 2; 0 to 9; 0 to 8; 0 to 7;0 to 6; 0 to 5; 0 to 4; 0 to 3; 0 to 2; 1 to 10; 1 to 9; 1 to 8; 1 to 7;1 to 6; 1 to 5; 1 to 4; 1 to 3; and 1 to 2. In other embodiments, the L*value for the polyesters useful in the invention can be present in oneof the following ranges: 50 to 60; 50 to 70; 50 to 80; 50 to 90; 60 to70; 60 to 80; 60 to 90; 70 to 80; 79 to 90.

In some embodiments, use of the polyester compositions useful in theinvention minimizes and/or eliminates the drying step prior to meltprocessing and/or thermoforming.

In one embodiment, polyesters of this invention exhibit superior notchedtoughness in thick sections. Notched Izod impact strength, as describedin ASTM D256, is a common method of measuring toughness. When tested bythe Izod method, polymers can exhibit either a complete break failuremode, where the test specimen breaks into two distinct parts, or apartial or no break failure mode, where the test specimen remains as onepart. The complete break failure mode is associated with low energyfailure. The partial and no break failure modes are associated with highenergy failure. A typical thickness used to measure Izod toughness is⅛″. At this thickness, very few polymers are believed to exhibit apartial or no break failure mode, polycarbonate being one notableexample. When the thickness of the test specimen is increased to ¼″,however, no commercial amorphous materials exhibit a partial or no breakfailure mode. In one embodiment, compositions of the present exampleexhibit a no break failure mode when tested in Izod using a ¼″ thickspecimen.

The polyesters useful in the invention exhibit a ductile-to-brittletransition temperature of less than 0° C. based on a 10-mil notch in a⅛-inch thick bar as defined by ASTM D256.

The polyester portion of the polyester composition useful in theinvention can be made by processes known from the literature such as,for example, by processes in homogenous solution, by transesterificationprocesses in the melt, and by two phase interfacial processes. Suitablemethods include the steps of reacting one or more dicarboxylic acidswith one or more glycols at a temperature of 100° C. to 315° C. at apressure of 0.1 to 760 mm Hg for a time sufficient to form a polyester.See U.S. Pat. No. 3,772,405 for methods of producing polyesters.

In a second aspect, the invention relates to medical devices comprisinga polyester produced by a process comprising:

-   -   (I) heating a mixture comprising the monomers useful in any of        the polyesters in the invention in the presence of a catalyst at        a temperature of 150 to 240° C. for a time sufficient to produce        an initial polyester;    -   (II) heating the initial polyester of step (I) at a temperature        of 240 to 320° C. for 1 to 4 hours; and    -   (III) removing any unreacted glycols.

Suitable catalysts for use in this process include, but are not limitedto, organo-zinc or tin compounds. The use of this type of catalyst iswell known in the art. Examples of catalysts useful in the presentinvention include, but are not limited to, zinc acetate, butyltintris-2-ethylhexanoate, dibutyltin diacetate, and/or dibutyltin oxide.Other catalysts may include, but are not limited to, those based ontitanium, zinc, manganese, lithium, germanium, and cobalt. Catalystamounts can range from 10 ppm to 20,000 ppm or 10 to 10,000 ppm, or 10to 5000 ppm or 10 to 1000 ppm or 10 to 500 ppm, or 10 to 300 ppm or 10to 250 based on the catalyst metal and based on the weight of the finalpolymer

Typically, step (I) is carried out until 50% by weight or more of the2,2,4,4-tetramethyl-1,3-cyclobutanediol has been reacted. Step (I) maybecarried out under pressure, ranging from atmospheric pressure to 100psig.

Typically, Step (II) and Step (III) can be conducted at the same time.These steps can be carried out by methods known in the art such as byplacing the reaction mixture under a pressure ranging, from 0.002 psigto atmospheric pressure, or by blowing hot nitrogen gas over themixture.

The invention further relates to a polyester product made by the processdescribed above.

The invention further relates to a polymer blend. The blend comprises:

-   -   (a) from 5 to 95 wt % of the polyesters described above; and    -   (b) from 5 to 95 wt % of a polymeric component.

Suitable examples of the polymeric components include, but are notlimited to, polyamides such as nylon; other polyesters different thanthose described herein; ZYTEL® from DuPont; polystyrene; polystyrenecopolymers; styrene acrylonitrile copolymers; acrylonitrile butadienestyrene copolymers; poly(methylmethacrylate); acrylic copolymers;poly(ether-imides) such as ULTEM® (a poly(ether-imide) from GeneralElectric); polyphenylene oxides such as poly(2,6-dimethylphenyleneoxide) or poly(phenylene oxide)/polystyrene blends such as NORYL 1000®(a blend of poly(2,6-dimethylphenylene oxide) and polystyrene resinsfrom General Electric); polyphenylene sulfides; polyphenylenesulfide/sulfones; poly(ester-carbonates); polycarbonates such as LEXAN®(a polycarbonate from General Electric); polysulfones; polysulfoneethers; and poly(ether-ketones) of aromatic dihydroxy compounds; ormixtures of any of the foregoing polymers. The blends can be prepared byconventional processing techniques known in the art, such as meltblending or solution blending. In one embodiment, polycarbonate is notpresent in the polyester composition. If polycarbonate is used in ablend in the polyester compositions of the invention, the blends can bevisually clear. The polyester compositions useful in the invention alsocontemplate the exclusion of polycarbonate as well as the inclusion ofpolycarbonate.

Polycarbonates useful in the invention may be prepared according toknown procedures by reacting the dihydroxyaromatic compound with acarbonate precursor such as phosgene, a haloformate or a carbonateester, a molecular weight regulator, an acid acceptor and a catalyst.Methods for preparing polycarbonates are known in the art and aredescribed, for example, in U.S. Pat. No. 4,452,933, which is herebyincorporated by reference herein.

Examples of suitable carbonate precursors include carbonyl bromide,carbonyl chloride, or mixtures thereof; diphenyl carbonate; adi(halophenyl)-carbonate, e.g., di(trichlorophenyl)carbonate,di(tribromophenyl)carbonate, and the like; di(alkylphenyl)carbonate,e.g., di(tolyl)carbonate; di(naphthyl)carbonate;di(chloronaphthyl)carbonate, or mixtures thereof; and bis-haloformatesof dihydric phenols.

Examples of suitable molecular weight regulators include, but are notlimited to, phenol, cyclohexanol, methanol, alkylated phenols, such asoctylphenol, para-tertiary-butyl-phenol, and the like. In oneembodiment, the molecular weight regulator is phenol or an alkylatedphenol.

The acid acceptor may be either an organic or an inorganic acidacceptor. A suitable organic acid acceptor is a tertiary amine andincludes such materials as pyridine, triethylamine, dimethylaniline,tributylamine, and the like. The inorganic acid acceptor can be either ahydroxide, a carbonate, a bicarbonate, or a phosphate of an alkali oralkaline earth metal.

The catalysts that can be used are those that typically aid thepolymerization of the monomer with phosgene. Suitable catalysts includetertiary amines such as triethylamine, tripropylamine,N,N-dimethylaniline, quaternary ammonium compounds such as, for example,tetraethylammonium bromide, cetyl triethyl ammonium bromide,tetra-n-heptylammonium iodide, tetra-n-propyl ammonium bromide,tetramethyl ammonium chloride, tetra-methyl ammonium hydroxide,tetra-n-butyl ammonium iodide, benzyltrimethyl ammonium chloride andquaternary phosphonium compounds such as, for example, n-butyltriphenylphosphonium bromide and methyltriphenyl phosphonium bromide.

The polycarbonates useful in the polyester compositions which are usefulin the invention also may be copolyestercarbonates such as thosedescribed in U.S. Pat. Nos. 3,169,121; 3,207,814; 4,194,038; 4,156,069;4,430,484, 4,465,820, and 4,981,898, all of which are incorporated byreference herein.

Copolyestercarbonates useful in this invention are availablecommercially. They are typically obtained by the reaction of at leastone dihydroxyaromatic compound with a mixture of phosgene and at leastone dicarboxylic acid chloride, especially isophthaloyl chloride,terephthaloyl chloride, or both.

In addition, the polyester compositions and the polymer blendcompositions useful in the medical devices of this invention may alsocontain from 0.1 to 25% by weight of the overall composition commonadditives such as colorants, mold release agents, flame retardants,plasticizers, nucleating agents, stabilizers, including but not limitedto, UV stabilizers, thermal stabilizers, fillers, and impact modifiers.Residues of such additives are also contemplated as part of thepolyester composition. Examples of typical commercially available impactmodifiers well known in the art and useful in this invention include,but are not limited to, ethylene/propylene terpolymers, styrene-basedblock copolymeric impact modifiers, and various acrylic core/shell typeimpact modifiers.

In addition, the polyester compositions and the polymer blendcompositions containing the polyesters of this invention may alsocontain from 0.01 to 25% by weight or 0.01 to 20% by weight or 0.01 to15% by weight or 0.01 to 10% by weight or 0.01 to 5% by weight of thetotal weight of the polyester composition of common additives such ascolorants, dyes, mold release agents, flame retardants, plasticizers,nucleating agents, stabilizers, including but not limited to, UVstabilizers, thermal stabilizers and/or reaction products thereof,fillers, and impact modifiers. Examples of typical commerciallyavailable impact modifiers well known in the art and useful in thisinvention include, but are not limited to, ethylene/propyleneterpolymers; functionalized polyolefins, such as those containing methylacrylate and/or glycidyl methacrylate; styrene-based block copolymericimpact modifiers; and various acrylic core/shell type impact modifiers.For example, UV additives can be incorporated into articles ofmanufacture through addition to the bulk, through application of a hardcoat, or through coextrusion of a cap layer. Residues of such additivesare also contemplated as part of the polyester composition.

The polyesters of the invention can comprise at least one chainextender. Suitable chain extenders include, but are not limited to,multifunctional (including, but not limited to, bifunctional)isocyanates, multifunctional epoxides, including for example, epoxylatednovolacs, and phenoxy resins. In certain embodiments, chain extendersmay be added at the end of the polymerization process or after thepolymerization process. If added after the polymerization process, chainextenders can be incorporated by compounding or by addition duringconversion processes such as injection molding or extrusion. The amountof chain extender used can vary depending on the specific monomercomposition used and the physical properties desired but is generallyabout 0.1 percent by weight to about 10 percent by weight, preferablyabout 0.1 to about 5 percent by weight, based on the total weight of thepolyester.

Thermal stabilizers are compounds that stabilize polyesters duringpolyester manufacture and/or post polymerization, including, but notlimited to, phosphorous compounds including but not limited tophosphoric acid, phosphorous acid, phosphonic acid, phosphinic acid,phosphonous acid, and various esters and salts thereof. These can bepresent in the polyester compositions useful in the invention. Theesters can be alkyl, branched alkyl, substituted alkyl, difunctionalalkyl, alkyl ethers, aryl, and substituted aryl. In one embodiment, thenumber of ester groups present in the particular phosphorous compoundcan vary from zero up to the maximum allowable based on the number ofhydroxyl groups present on the thermal stabilizer used. The term“thermal stabilizer” is intended to include the reaction product(s)thereof. The term “reaction product” as used in connection with thethermal stabilizers of the invention refers to any product of apolycondensation or esterification reaction between the thermalstabilizer and any of the monomers used in making the polyester as wellas the product of a polycondensation or esterification reaction betweenthe catalyst and any other type of additive.

Reinforcing materials may be useful in the compositions of thisinvention. The reinforcing materials may include, but are not limitedto, carbon filaments, silicates, mica, clay, talc, titanium dioxide,Wollastonite, glass flakes, glass beads and fibers, and polymeric fibersand combinations thereof. In one embodiment, the reinforcing materialsare glass, such as, fibrous glass filaments, mixtures of glass and talc,glass and mica, and glass and polymeric fibers.

The invention further relates to medical devices described herein. Themethods of forming the polyesters into medical devices are well known inthe art. Examples of medical devices include but are not limited tomedical bottles. These medical bottles include but are not limited toinjection blow molded bottles, injection stretch blow molded bottles,extrusion blow molded bottles, and extrusion stretch blow moldedbottles. Methods of making bottles include but are not limited toextrusion blow molding, extrusion stretch blow molding, injection blowmolding, and injection stretch blow molding.

In another embodiment, the invention further relates to medical devicescomprising articles of manufacture comprising any of the polyesters andblends described herein extruded, calendered, and/or molded articlesincluding but not limited to, injection molded articles, extrudedarticles, cast extrusion articles, profile extrusion articles, melt spunarticles, thermoformed articles, extrusion molded articles, injectionblow molded articles, injection stretch blow molded articles, extrusionblow molded articles, and extrusion stretch blow molded articles. Thesearticles can include, but are not limited, to films, bottles (including,but not limited to, baby bottles), containers, sheet and/or fibers.

The methods of forming the polyesters into fibers, films, moldedarticles, containers, and sheeting are well known in the art. Examplesof potential molded articles include without limitation: medical devicessuch as dialysis equipment, medical packaging, healthcare supplies,commercial foodservice products such as food pans, steam trays, tumblersand storage boxes, baby bottles, food processors, blender and mixerbowls, utensils, water bottles, crisper trays, washing machine fronts,and vacuum cleaner parts. Other potential molded articles could include,but are not limited to, ophthalmic lenses and frames. For instance, thismaterial can be used to make bottles, including, but not limited to,baby bottles, as it is clear, tough, heat resistant, and displays goodhydrolytic stability.

In another embodiment, the invention further relates to medical devicescomprising articles of manufacture comprising the film(s) and/orsheet(s) containing polyester compositions described herein.

The films and/or sheets useful in the present invention can be of anythickness which would be apparent to one of ordinary skill in the art.In one embodiment, the film(s) useful in the invention have a thicknessof no more than 40 mils. In one embodiment, the film(s) of the inventionhave a thickness of no more than 35 mils. In one embodiment, the film(s)useful in the invention have a thickness of no more than 30 mils. In oneembodiment, the film(s) of the invention have a thickness of no morethan 25 mils. In one embodiment, the film(s) of the invention have athickness of no more than 20 mils.

In one embodiment, the sheet(s) of the invention have a thickness of noless than 20 mils. In another embodiment, the sheet(s) of the inventionhave a thickness of no less than 25 mils. In another embodiment, thesheet(s) of the invention have a thickness of no less than 30 mils. Inanother embodiment, the sheet(s) of the invention have a thickness of noless than 35 mils. In another embodiment, the sheet(s) of the inventionhave a thickness of no less than 40 mils.

The invention further relates to the film(s) and/or sheet(s) comprisingthe polyester compositions of the invention. The methods of forming thepolyesters into film(s) and/or sheet(s) are well known in the art.Examples of film(s) and/or sheet(s) of the invention including but notlimited to extruded film(s) and/or sheet(s), calendered film(s) and/orsheet(s), compression molded film(s) and/or sheet(s), solution castedfilm(s) and/or sheet(s). Methods of making film and/or sheet include butare not limited to extrusion, calendering, compression molding, andsolution casting.

In one embodiment the present invention relates to medical devices, suchas lab-ware and components of diagnostic test kits, that may come intocontact with biological fluids or biological systems and that have areduced interaction with that biological fluid or system. Medicaldevices include, but are not limited to, diagnostic equipment, suchtubes, bottles, bags, and other containers; fluid handling apparatus,such as intravenous (IV) systems including needles and hubs, cannulae,tubing, connectors and other fixtures; blood treatment and dialysisequipment, including dialyzers, filters, and oxygenators; anesthesia andrespiratory therapy equipment, such as masks and tubing; drug deliveryand packaging supplies, such as syringes, tubing, transdermal patches,inhalers, bags and bottles; catheters, tubes, and endoscopy equipment;and labware, including dishes, vials, plates and cell culture equipment.The devices comprise a UV-cured silicone polymer coating, which isapplied to a surface of the device so as to reduce the response of thebiological fluid or system in contact with the device. The resultantdevices possess a thin, adherent coating of silicone polymer which givesbiocompatibility. By using a coating, the advantageous properties of thesubstrate material may be obtained, which may include stiffness,clarity, favorable economics or other desirable properties. In anotherembodiment the present invention relates to a method of reducing theinteraction between a medical device comprising any of the polyesterscomprising a cyclobutanediol described above and a biological fluid orsystem, the method comprising coating at least a portion of a surface ofthe device with a UV-curable silicone polymer composition and exposingat least a portion of the silicone polymer composition to ultravioletlight to cure the composition.

The UV-curable silicone polymer composition can be applied to nearly anysubstrate known in the art for use in medical devices. Such substratesinclude, for example, plastics, elastomers, metals and the like.Specific materials include polyvinylchlorides (PVC), polycarbonates(PC), polyurethanes (PU), polypropylenes (PP), polyethylenes (PE),silicones, polyesters, cellulose acetates, polymethylmethacrylates(PMMA), hydroxyethylmethacrylates, N-vinyl pyrrolidones, fluorinatedpolymers such as polytetrafluoroethylene, polyamides, polystyrenes,copolymers or mixtures of the above polymers and medical grade metalssuch as steel or titanium.

Examples of UV-curable silicone polymers that can be used in the coatingcomposition of the invention include polymers composed of at least 50mole % dimethyl siloxane repeat units. Other suitable UV-curablesilicone polymers are known in the art such as those mentioned in U.S.Pat. Nos. 4,576,999; 4,279,717; 4,421,904; 4,547,431; 4,576,999; and4,977,198; the entire contents of which are hereby incorporated byreference.

The coating composition may be applied by any number of methods,including but not limited to spraying, dipping, printing, orflow-coating. Other methods of application known in the art are also tobe considered within the scope of this invention. Further, the polymermay be used in solution or emulsified to reduce its viscosity forapplication. A diluent, if employed, may be allowed to evaporate, andthis evaporation may be facilitated by applying energy via heat orradiation. Optionally, evaporation of all or part of the solvent may beaccomplished after a curing operation.

Any solvent that is capable of dissolving or substantially dissolvingthe silicone polymer such that its viscosity is reduced for applicationmay be used. Examples of such solvents include aliphatic or aromatichydrocarbons, such as toluene and cyclohexane; volative silicones suchas cyclomethicone; chlorinated hydrocarbons; and esters (see, e.g.,Polymer Handbook, Brandup and Immergut, Eds., 2nd edition, page IV-253(1975)). In addition, the viscosity of the coatings could be decreasedthrough emulsification, or lowering the molecular weight of thesilicones.

The silicone polymer coating composition may further include one or moreUV curing agents to help facilitate curing of the composition. SuitableUV curing agents may be obtained commercially from vendors of theUV-curable silicone polymers such as General Electric Co. Suitable UVcuring agents are also known in the art such as in U.S. Pat. Nos.4,576,999; 4,279,717; 4,421,904; 4,547,431; 4,576,999; and 4,977,198.

Curing of the coating may be achieved by exposure to UV radiation, whichmay be produced by any convenient means. The curing time depends on anumber of factors including the precise polymer composition and thedesired degree of cross-linking. Preferably, the curing time is lessthan 5 seconds.

The finished coating may have a range of thicknesses, from severalnanometers up to several millimeters, preferably from 0.1 to 100micrometers. Similarly, the substrate thickness may vary, from about0.001 millimeters to about 100 millimeters, preferably from about 0.01millimeters to about 10 millimeters.

The ability to cure using ultraviolet light rather than a thermallycured polysiloxane is desirable in areas in which the substrate might besensitive to elevated temperatures. For devices used in medicalapplications, this is a common concern as not all materials canwithstand elevated temperature in procedures such as steamsterilization. For temperature-sensitive substrates, other sterilizationmethods can be used that do not involve the application of heat, such asgamma irradiation or ethylene oxide treatment. The use of UV curingpolysiloxanes according to the present invention allows these sametemperature-sensitive substrates to be made biocompatible. By“temperature-sensitive substrates,” it is meant substrates that canirreversibly change their characteristics (such as dimensions, shape,color, brittleness, crystallinity, etc.) at elevated temperaturestypically employed in medical or diagnostic applications. Examples ofsuch substrates include polymers having relatively low softening,melting, or glass transition temperature points.

Additionally, by crosslinking the coating using UV radiation, patternedsurfaces may be formed. In this way, selective areas may be made toresist protein adsorption, while other areas may be receptive to proteinadsorption. By exposing selected areas to UV light, the non-exposed,non-crosslinked areas may be subsequently removed by various techniques,such as solvent washing. This could produce patterned areas ofrelatively low and high protein binding, for analytical tests and otherapplications.

An embodiment of the present invention is further illustrated by thefollowing examples. It will be apparent to those skilled in the art thatvarious modifications and variations can be made in the presentinvention without departing from the scope or spirit of the invention.Other embodiments of the invention will be apparent to those skilled inthe art from consideration of the specification and practice of theinvention disclosed herein. It is intended that the specification andexamples be considered as exemplary only, with a true scope and spiritof the invention being indicated by the following claims. Moreover, allpatents, patent application (published and unpublished, foreign ordomestic), literature references or other publications noted above areincorporated herein by reference for any disclosure pertinent to thepractice of this invention.

The following examples further illustrate how the medical devices of theinvention can be made and evaluated, and are intended to be purelyexemplary of the invention and are not intended to limit the scopethereof. Unless indicated otherwise, parts are parts by weight,temperature is in degrees C. or is at room temperature, and pressure isat or near atmospheric.

EXAMPLES

Measurement Methods

The inherent viscosity of the polyesters was determined in 60/40 (wt/wt)phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at 25° C.

Unless stated otherwise, the glass transition temperature (T_(g)) wasdetermined using a TA DSC 2920 instrument from Thermal AnalystInstruments at a scan rate of 20° C./min according to ASTM D3418.

The glycol content and the cis/trans ratio of the compositions weredetermined by proton nuclear magnetic resonance (NMR) spectroscopy. AllNMR spectra were recorded on a JEOL Eclipse Plus 600 MHz nuclearmagnetic resonance spectrometer using either chloroform-trifluoroaceticacid (70-30 volume/volume) for polymers or, for oligomeric samples,60/40 (wt/wt) phenol/tetrachloroethane with deuterated chloroform addedfor lock. Peak assignments for 2,2,4,4-tetramethyl-1,3-cyclobutanediolresonances were made by comparison to model mono- and dibenzoate estersof 2,2,4,4-tetramethyl-1,3-cyclobutanediol. These model compoundsclosely approximate the resonance positions found in the polymers andoligomers.

The crystallization half-time, t1/2, was determined by measuring thelight transmission of a sample via a laser and photo detector as afunction of time on a temperature controlled hot stage. This measurementwas done by exposing the polymers to a temperature, T_(max), and thencooling it to the desired temperature. The sample was then held at thedesired temperature by a hot stage while transmission measurements weremade as a function of time. Initially, the sample was visually clearwith high light transmission and became opaque as the samplecrystallized. The crystallization half-time was recorded as the time atwhich the light transmission was halfway between the initialtransmission and the final transmission. T_(max) is defined as thetemperature required to melt the crystalline domains of the sample (ifcrystalline domains are present). The T_(max) reported in the examplesbelow represents the temperature at which each sample was heated tocondition the sample prior to crystallization half time measurement. TheT_(max) temperature is dependant on composition and is typicallydifferent for each polyester. For example, PCT may need to be heated tosome temperature greater than 290° C. to melt the crystalline domains.

Density was determined using a gradient density column at 23° C.

The melt viscosity reported herein was measured by using a RheometricsDynamic Analyzer (RDA II). The melt viscosity was measured as a functionof shear rate, at frequencies ranging from 1 to 400 rad/sec, at thetemperatures reported. The zero shear melt viscosity (η_(o)) is the meltviscosity at zero shear rate estimated by extrapolating the data byknown models in the art. This step is automatically performed by theRheometrics Dynamic Analyzer (RDA II) software.

The polymers were dried at a temperature ranging from 80 to 100° C. in avacuum oven for 24 hours and injection molded on a Boy 22S moldingmachine to give ⅛×½×5-inch and ¼×½×5-inch flexure bars. These bars werecut to a length of 2.5 inch and notched down the ½ inch width with a10-mil notch in accordance with ASTM D256. The average Izod impactstrength at 23° C. was determined from measurements on 5 specimens.

In addition, 5 specimens were tested at various temperatures using 5° C.increments in order to determine the brittle-to-ductile transitiontemperature. The brittle-to-ductile transition temperature is defined asthe temperature at which 50% of the specimens fail in a brittle manneras denoted by ASTM D256.

Color values reported herein were determined using a Hunter LabUltrascan Spectra Colorimeter manufactured by Hunter Associates LabInc., Reston, Va. The color determinations were averages of valuesmeasured on either pellets of the polyesters or plaques or other itemsinjection molded or extruded from them. They were determined by theL*a*b* color system of the CIE (International Commission onIllumination) (translated), wherein L* represents the lightnesscoordinate, a* represents the red/green coordinate, and b* representsthe yellow/blue coordinate.

In addition, 10-mil films were compression molded using a Carver pressat 240° C.

Unless otherwise specified, the cis/trans ratio of the 1,4cyclohexanedimethanol used in the following examples was approximately30/70, and could range from 35/65 to 25/75. Unless otherwise specified,the cis/trans ratio of the 2,2,4,4-tetramethyl-1,3-cyclobutanediol usedin the following examples was approximately 50/50.

The following abbreviations apply throughout the working examples andfigures: TPA Terephthalic acid DMT Dimethyl terephthalate TMCD2,2,4,4-tetramethyl-1,3-cyclobutanediol CHDM 1,4-cyclohexanedimethanolIV Inherent viscosity η_(o) Zero shear melt viscosity T_(g) Glasstransition temperature T_(bd) Brittle-to-ductile transition temperatureT_(max) Conditioning temperature for crystallization half timemeasurements

Example 1

This example illustrates that 2,2,4,4-tetramethyl-1,3-cyclobutanediol ismore effective at reducing the crystallization rate of PCT than ethyleneglycol or isophthalic acid. In addition, this example illustrates thebenefits of 2,2,4,4-tetramethyl-1,3-cyclobutanediol on the glasstransition temperature and density.

A variety of copolyesters were prepared as described below. Thesecopolyesters were all made with 200 ppm dibutyl tin oxide as thecatalyst in order to minimize the effect of catalyst type andconcentration on nucleation during crystallization studies. Thecis/trans ratio of the 1,4-cyclohexanedimethanol was 31/69 while thecis/trans ratio of the 2,2,4,4-tetramethyl-1,3-cyclobutanediol isreported in Table 1.

For purposes of this example, the samples had sufficiently similarinherent viscosities thereby effectively eliminating this as a variablein the crystallization rate measurements.

Crystallization half-time measurements from the melt were made attemperatures from 140 to 200° C. at 10° C. increments and are reportedin Table 1. The fastest crystallization half-time for each sample wastaken as the minimum value of crystallization half-time as a function oftemperature, typically occurring around 170 to 180° C. The fastestcrystallization half-times for the samples are plotted in FIG. 1 as afunction of mole % comonomer modification to PCT.

The data shows that 2,2,4,4-tetramethyl-1,3-cyclobutanediol is moreeffective than ethylene glycol and isophthalic acid at decreasing thecrystallization rate (i.e., increasing the crystallization half-time).In addition, 2,2,4,4-tetramethyl-1,3-cyclobutanediol increases T_(g) andlowers density. TABLE 1 Crystallization Half-times (min) at at at at atat at Comonomer IV Density T_(g) T_(max) 140° C. 150° C. 160° C. 170° C.180° C. 190° C. 200° C. Example (mol %)¹ (dl/g) (g/ml) (° C.) (° C.)(min) (min) (min) (min) (min) (min) (min) 1A 20.2% A² 0.630 1.198 87.5290 2.7 2.1 1.3 1.2 0.9 1.1 1.5 1B 19.8% B 0.713 1.219 87.7 290 2.3 2.51.7 1.4 1.3 1.4 1.7 1C 20.0% C 0.731 1.188 100.5 290 >180 >60 35.0 23.321.7 23.3 25.2 1D 40.2% A² 0.674 1.198 81.2 260 18.7 20.0 21.3 25.0 34.059.9 96.1 1E 34.5% B 0.644 1.234 82.1 260 8.5 8.2 7.3 7.3 8.3 10.0 11.41F 40.1% C 0.653 1.172 122.0 260 >10 days >5 days >5 days 19204 >5days >5 days >5 days 1G 14.3% D 0.646³ 1.188 103.0 290 55.0 28.8 11.66.8 4.8 5.0 5.5 1H 15.0% E 0.728⁴ 1.189 99.0 290 25.4 17.1 8.1 5.9 4.32.7 5.1¹The balance of the diol component of the polyesters in Table 1 is1,4-cyclohexanedimethanol; and the balance of the dicarboxylic acidcomponent of the polyesters in Table 1 is dimethyl terephthalate; if thedicarboxylic acid is not described, it is 100 mole % dimethylterephthalate.²100 mole % 1,4-cyclohexanedimethanol.³A film was pressed from the ground polyester of Example 1G at 240° C.The resulting film had an inherent viscosity value of 0.575 dL/g.⁴A film was pressed from the ground polyester of Example 1H at 240° C.The resulting film had an inherent viscosity value of 0.0.652 dL/g.where:A is Isophthalic AcidB is Ethylene GlycolC is 2,2,4,4-Tetramethyl-1,3-cyclobutanediol (approx. 50/50 cis/trans)D is 2,2,4,4-Tetramethyl-1,3-cyclobutanediol (98/2 cis/trans)E is 2,2,4,4-Tetramethyl-1,3-cyclobutanediol (5/95 cis/trans)

As shown in Table 1 and FIG. 1, 2,2,4,4-tetramethyl-1,3-cyclobutanediolis more effective than other comonomers, such ethylene glycol andisophthalic acid, at increasing the crystallization half-time, i.e., thetime required for a polymer to reach half of its maximum crystallinity.By decreasing the crystallization rate of PCT (increasing thecrystallization half-time), amorphous articles based on2,2,4,4-tetramethyl-1,3-cyclobutanediol-modified PCT as described hereinmay be fabricated by methods known in the art. As shown in Table 1,these materials can exhibit higher glass transition temperatures andlower densities than other modified PCT copolyesters.

Preparation of the polyesters shown on Table 1 is described below.

Example 1A

This example illustrates the preparation of a copolyester with a targetcomposition of 80 mol % dimethyl terephthalate residues, 20 mol %dimethyl isophthalate residues, and 100 mol % 1,4-cyclohexanedimethanolresidues (28/72 cis/trans).

A mixture of 56.63 g of dimethyl terephthalate, 55.2 g of1,4-cyclohexanedimethanol, 14.16 g of dimethyl isophthalate, and 0.0419g of dibutyl tin oxide was placed in a 500-milliliter flask equippedwith an inlet for nitrogen, a metal stirrer, and a short distillationcolumn. The flask was placed in a Wood's metal bath already heated to210° C. The stirring speed was set to 200 RPM throughout the experiment.The contents of the flask were heated at 210° C. for 5 minutes and thenthe temperature was gradually increased to 290° C. over 30 minutes. Thereaction mixture was held at 290° C. for 60 minutes and then vacuum wasgradually applied over the next 5 minutes until the pressure inside theflask reached 100 mm of Hg. The pressure inside the flask was furtherreduced to 0.3 mm of Hg over the next 5 minutes. A pressure of 0.3 mm ofHg was maintained for a total time of 90 minutes to remove excessunreacted diols. A high melt viscosity, visually clear and colorlesspolymer was obtained with a glass transition temperature of 87.5° C. andan inherent viscosity of 0.63 dL/g. NMR analysis showed that the polymerwas composed of 100 mol % 1,4-cyclohexanedimethanol residues and 20.2mol % dimethyl isophthalate residues.

Example 1B

This example illustrates the preparation of a copolyester with a targetcomposition of 100 mol % dimethyl terephthalate residues, 20 mol %ethylene glycol residues, and 80 mol % 1,4-cyclohexanedimethanolresidues (32/68 cis/trans).

A mixture of 77.68 g of dimethyl terephthalate, 50.77 g of1,4-cyclohexanedimethanol, 27.81 g of ethylene glycol, and 0.0433 g ofdibutyl tin oxide was placed in a 500-milliliter flask equipped with aninlet for nitrogen, a metal stirrer, and a short distillation column.The flask was placed in a Wood's metal bath already heated to 200° C.The stirring speed was set to 200 RPM throughout the experiment. Thecontents of the flask were heated at 200° C. for 60 minutes and then thetemperature was gradually increased to 210° C. over 5 minutes. Thereaction mixture was held at 210° C. for 120 minutes and then heated upto 280° C. in 30 minutes. Once at 280° C., vacuum was gradually appliedover the next 5 minutes until the pressure inside the flask reached 100mm of Hg. The pressure inside the flask was further reduced to 0.3 mm ofHg over the next 10 minutes. A pressure of 0.3 mm of Hg was maintainedfor a total time of 90 minutes to remove excess unreacted diols. A highmelt viscosity, visually clear and colorless polymer was obtained with aglass transition temperature of 87.7° C. and an inherent viscosity of0.71 dL/g. NMR analysis showed that the polymer was composed of 19.8 mol% ethylene glycol residues.

Example 1C

This example illustrates the preparation of a copolyester with a targetcomposition of 100 mol % dimethyl terephthalate residues, 20 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues, and 80 mol %1,4-cyclohexanedimethanol residues (31/69 cis/trans).

A mixture of 77.68 g of dimethyl terephthalate, 48.46 g of1,4-cyclohexanedimethanol, 17.86 g of2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 0.046 g of dibutyl tinoxide was placed in a 500-milliliter flask equipped with an inlet fornitrogen, a metal stirrer, and a short distillation column. Thispolyester was prepared in a manner similar to that described in Example1A. A high melt viscosity, visually clear and colorless polymer wasobtained with a glass transition temperature of 100.5° C. and aninherent viscosity of 0.73 dL/g. NMR analysis showed that the polymerwas composed of 80.5 mol % 1,4-cyclohexanedimethanol residues and 19.5mol % 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.

Example 1D

This example illustrates the preparation of a copolyester with a targetcomposition of 100 mol % dimethyl terephthalate residues, 40 mol %dimethyl isophthalate residues, and 100 mol % 1,4-cyclohexanedimethanolresidues (28/72 cis/trans).

A mixture of 42.83 g of dimethyl terephthalate, 55.26 g of1,4-cyclohexanedimethanol, 28.45 g of dimethyl isophthalate, and 0.0419g of dibutyl tin oxide was placed in a 500-milliliter flask equippedwith an inlet for nitrogen, a metal stirrer, and a short distillationcolumn. The flask was placed in a Wood's metal bath already heated to210° C. The stirring speed was set to 200 RPM throughout the experiment.The contents of the flask were heated at 210° C. for 5 minutes and thenthe temperature was gradually increased to 290° C. over 30 minutes. Thereaction mixture was held at 290° C. for 60 minutes and then vacuum wasgradually applied over the next 5 minutes until the pressure inside theflask reached 100 mm of Hg. The pressure inside the flask was furtherreduced to 0.3 mm of Hg over the next 5 minutes. A pressure of 0.3 mm ofHg was maintained for a total time of 90 minutes to remove excessunreacted diols. A high melt viscosity, visually clear and colorlesspolymer was obtained with a glass transition temperature of 81.2° C. andan inherent viscosity of 0.67 dL/g. NMR analysis showed that the polymerwas composed of 100 mol % 1,4-cyclohexanedimethanol residues and 40.2mol % dimethyl isophthalate residues.

Example 1E

This example illustrates the preparation of a copolyester with a targetcomposition of 100 mol % dimethyl terephthalate residues, 40 mol %ethylene glycol residues, and 60 mol % 1,4-cyclohexanedimethanolresidues (31/69 cis/trans).

A mixture of 81.3 g of dimethyl terephthalate, 42.85 g of1,4-cyclohexanedimethanol, 34.44 g of ethylene glycol, and 0.0419 g ofdibutyl tin oxide was placed in a 500-milliliter flask equipped with aninlet for nitrogen, a metal stirrer, and a short distillation column.The flask was placed in a Wood's metal bath already heated to 200° C.The stirring speed was set to 200 RPM throughout the experiment. Thecontents of the flask were heated at 200° C. for 60 minutes and then thetemperature was gradually increased to 210° C. over 5 minutes. Thereaction mixture was held at 210° C. for 120 minutes and then heated upto 280° C. in 30 minutes. Once at 280° C., vacuum was gradually appliedover the next 5 minutes until the pressure inside the flask reached 100mm of Hg. The pressure inside the flask was further reduced to 0.3 mm ofHg over the next 10 minutes. A pressure of 0.3 mm of Hg was maintainedfor a total time of 90 minutes to remove excess unreacted diols. A highmelt viscosity, visually clear and colorless polymer was obtained with aglass transition temperature of 82.1° C. and an inherent viscosity of0.64 dL/g. NMR analysis showed that the polymer was composed of 34.5 mol% ethylene glycol residues.

Example 1F

This example illustrates the preparation of a copolyester with a targetcomposition of 100 mol % dimethyl terephthalate residues, 40 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues, and 60 mol %1,4-cyclohexanedimethanol residues (31/69 cis/trans).

A mixture of 77.4 g of dimethyl terephthalate, 36.9 g of1,4-cyclohexanedimethanol, 32.5 g of2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 0.046 g of dibutyl tinoxide was placed in a 500-milliliter flask equipped with an inlet fornitrogen, a metal stirrer, and a short distillation column. The flaskwas placed in a Wood's metal bath already heated to 210° C. The stirringspeed was set to 200 RPM throughout the experiment. The contents of theflask were heated at 210° C. for 3 minutes and then the temperature wasgradually increased to 260° C. over 30 minutes. The reaction mixture washeld at 260° C. for 120 minutes and then heated up to 290° C. in 30minutes. Once at 290° C., vacuum was gradually applied over the next 5minutes until the pressure inside the flask reached 100 mm of Hg. Thepressure inside the flask was further reduced to 0.3 mm of Hg over thenext 5 minutes. A pressure of 0.3 mm of Hg was maintained for a totaltime of 90 minutes to remove excess unreacted diols. A high meltviscosity, visually clear and colorless polymer was obtained with aglass transition temperature of 122° C. and an inherent viscosity of0.65 dL/g. NMR analysis showed that the polymer was composed of 59.9 mol% 1,4-cyclohexanedimethanol residues and 40.1 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.

Example 1G

This example illustrates the preparation of a copolyester with a targetcomposition of 100 mol % dimethyl terephthalate residues, 20 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues (98/2 cis/trans), and80 mol % 1,4-cyclohexanedimethanol residues (31/69 cis/trans).

A mixture of 77.68 g of dimethyl terephthalate, 48.46 g of1,4-cyclohexanedimethanol, 20.77 g of2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 0.046 g of dibutyl tinoxide was placed in a 500-milliliter flask equipped with an inlet fornitrogen, a metal stirrer, and a short distillation column. The flaskwas placed in a Wood's metal bath already heated to 210° C. The stirringspeed was set to 200 RPM throughout the experiment. The contents of theflask were heated at 210° C. for 3 minutes and then the temperature wasgradually increased to 260° C. over 30 minutes. The reaction mixture washeld at 260° C. for 120 minutes and then heated up to 290° C. in 30minutes. Once at 290° C., vacuum was gradually applied over the next 5minutes until the pressure inside the flask reached 100 mm of Hg and thestirring speed was also reduced to 100 RPM. The pressure inside theflask was further reduced to 0.3 mm of Hg over the next 5 minutes andthe stirring speed was reduced to 50 RPM. A pressure of 0.3 mm of Hg wasmaintained for a total time of 60 minutes to remove excess unreacteddiols. A high melt viscosity, visually clear and colorless polymer wasobtained with a glass transition temperature of 103° C. and an inherentviscosity of 0.65 dL/g. NMR analysis showed that the polymer wascomposed of 85.7 mol % 1,4-cyclohexanedimethanol residues and 14.3 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.

Example 1H

This example illustrates the preparation of a copolyester with a targetcomposition of 100 mol % dimethyl terephthalate residues, 20 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues (5/95 cis/trans), and80 mol % 1,4-cyclohexanedimethanol residues (31/69 cis/trans).

A mixture of 77.68 g of dimethyl terephthalate, 48.46 g of1,4-cyclohexanedimethanol, 20.77 g of2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 0.046 g of dibutyl tinoxide was placed in a 500-milliliter flask equipped with an inlet fornitrogen, a metal stirrer, and a short distillation column. The flaskwas placed in a Wood's metal bath already heated to 210° C. The stirringspeed was set to 200 RPM at the beginning of the experiment. Thecontents of the flask were heated at 210° C. for 3 minutes and then thetemperature was gradually increased to 260° C. over 30 minutes. Thereaction mixture was held at 260° C. for 120 minutes and then heated upto 290° C. in 30 minutes. Once at 290° C., vacuum was gradually appliedover the next 5 minutes with a set point of 100 mm of Hg and thestirring speed was also reduced to 100 RPM. The pressure inside theflask was further reduced to a set point of 0.3 mm of Hg over the next 5minutes and the stirring speed was reduced to 50 RPM. This pressure wasmaintained for a total time of 60 minutes to remove excess unreacteddiols. It was noted that the vacuum system failed to reach the set pointmentioned above, but produced enough vacuum to produce a high meltviscosity, visually clear and colorless polymer with a glass transitiontemperature of 99° C. and an inherent viscosity of 0.73 dL/g. NMRanalysis showed that the polymer was composed of 85 mol %1,4-cyclohexanedimethanol residues and 15 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.

Example 2

This example illustrates that 2,2,4,4-tetramethyl-1,3-cyclobutanediolimproves the toughness of PCT-based copolyesters (polyesters containingterephthalic acid and 1,4-cyclohexanedimethanol).

Copolyesters based on 2,2,4,4-tetramethyl-1,3-cyclobutanediol wereprepared as described below. The cis/trans ratio of the1,4-cyclohexanedimethanol was approximately 31/69 for all samples.Copolyesters based on ethylene glycol and 1,4-cyclohexanedimethanol werecommercial polyesters. The copolyester of Example 2A (Eastar PCTG 5445)was obtained from Eastman Chemical Co. The copolyester of Example 2B wasobtained from Eastman Chemical Co. under the trade name Spectar. Example2C and Example 2D were prepared on a pilot plant scale (each a 15-lbbatch) following an adaptation of the procedure described in Example 1Aand having the inherent viscosities and glass transition temperaturesdescribed in Table 2 below. Example 2C was prepared with a target tinamount of 300 ppm (Dibutyltin Oxide). The final product contained 295ppm tin. The color values for the polyester of Example 2C were L*=77.11;a*=−1.50; and b*=5.79. Example 2D was prepared with a target tin amountof 300 ppm (Dibutyltin Oxide). The final product contained 307 ppm tin.The color values for the polyester of Example 2D were L*=66.72;a*=−1.22; and b*=16.28.

Materials were injection molded into bars and subsequently notched forIzod testing. The notched Izod impact strengths were obtained as afunction of temperature and are also reported in Table 2.

For a given sample, the Izod impact strength undergoes a majortransition in a short temperature span. For instance, the Izod impactstrength of a copolyester based on 38 mol % ethylene glycol undergoesthis transition between 15 and 20° C. This transition temperature isassociated with a change in failure mode; brittle/low energy failures atlower temperatures and ductile/high energy failures at highertemperatures. The transition temperature is denoted as thebrittle-to-ductile transition temperature, T_(bd), and is a measure oftoughness. T_(bd) is reported in Table 2 and plotted against mol %comonomer in FIG. 2.

The data shows that adding 2,2,4,4-tetramethyl-1,3-cyclobutanediol toPCT lowers T_(bd) and improves the toughness, as compared to ethyleneglycol, which increases T_(bd) of PCT. TABLE 2 Notched Izod ImpactEnergy (ft-lb/in) Ex- Comonomer IV T_(g) T_(bd) at at at at at at at atat ample (mol %)¹ (dl/g) (° C.) (° C.) −20° C. −15° C. −10° C. −5° C. at0° C. at 5° C. 10° C. 15° C. 20° C. 25° C. 30° C. 2A 38.0% B 0.68 86 18NA NA NA 1.5 NA NA 1.5 1.5 32 32 NA 2B 69.0% B 0.69 82 26 NA NA NA NA NANA 2.1 NA 2.4 13.7 28.7 2C 22.0% C 0.66 106 −5 1.5 NA 12 23 23 NA 23 NANA NA NA 2D 42.8% C 0.60 133 −12 2.5 2.5 11 NA 14 NA NA NA NA NA NA¹The balance of the glycol component of the polyesters in the Table is1,4-cyclohexanedimethanol. All polymers were prepared from 100 mole %dimethyl terephthalate.NA = Not available.where:B is Ethylene glycolC is 2,2,4,4-Tetramethyl-1,3-cyclobutanediol (50/50 cis/trans)

Example 3

This example illustrates that 2,2,4,4-tetramethyl-1,3-cyclobutanediolcan improve the toughness of PCT-based copolyesters (polyesterscontaining terephthalic acid and 1,4-cyclohexanedimethanol). Polyestersprepared in this example comprise from 15 to 25 mol % of2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.

Copolyesters based on dimethyl terephthalate,2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 1,4-cyclohexanedimethanolwere prepared as described below, having the composition and propertiesshown on Table 3. The balance up to 100 mol % of the diol component ofthe polyesters in Table 3 was 1,4-cyclohexanedimethanol (31/69cis/trans).

Materials were injection molded into both 3.2 mm and 6.4 mm thick barsand subsequently notched for Izod impact testing. The notched Izodimpact strengths were obtained at 23° C. and are reported in Table 3.Density, Tg, and crystallization halftime were measured on the moldedbars. Melt viscosity was measured on pellets at 290° C. TABLE 3Compilation of various properties for certain polyesters useful in theinvention Notched Notched Izod of Izod of 3.2 mm 6.4 mm Melt thick thickCrystallization Viscosity Pellet Molded bars at bars at SpecificHalftime from at 1 rad/sec TMCD % cis IV Bar IV 23° C. 23° C. Gravity Tgmelt at 170° C. at 290° C. Example mole % TMCD (dl/g) (dl/g) (J/m) (J/m)(g/mL) (° C.) (min) (Poise) A 15 48.8 0.736 0.707 1069 878 1.184 104 155649 B 18 NA 0.728 0.715 980 1039 1.183 108 22 6621 C 20 NA 0.706 0.6961006 1130 1.182 106 52 6321 D 22 NA 0.732 0.703 959 988 1.178 108 637161 E 21 NA 0.715 0.692 932 482 1.179 110 56 6162 F 24 NA 0.708 0.677976 812 1.180 109 58 6282 G 23 NA 0.650 0.610 647 270 1.182 107 46 3172H 23 47.9 0.590 0.549 769 274 1.181 106 47 1736 I 23 48.1 0.531 0.516696 352 1.182 105 19 1292 J 23 47.8 0.364 NA NA NA NA  98 NA 167NA = Not available.

Example 3A

21.24 lb (49.71 gram-mol) dimethyl terephthalate, 14.34 lb (45.21gram-mol) 1,4-cyclohexanedimethanol, and 4.58 lb (14.44 gram-mol)2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted together in thepresence of 200 ppm of the catalyst butyltin tris(2-ethylhexanoate). Thereaction was carried out under a nitrogen gas purge in an 18-gallonstainless steel pressure vessel fitted with a condensing column, avacuum system, and a HELICONE-type agitator. With the agitator runningat 25 RPM, the reaction mixture temperature was increased to 250° C. andthe pressure was increased to 20 psig. The reaction mixture was held for2 hours at 250° C. and at a pressure of 20 psig. The pressure was thendecreased to 0 psig at a rate of 3 psig/minute. The temperature of thereaction mixture was then increased to 270° C. and the pressure wasdecreased to 90 mm of Hg. After a 1 hour hold time at 270° C. and 90 mmof Hg, the agitator speed was decreased to 15 RPM, the reaction mixturetemperature was increased to 290° C., and the pressure was decreased to<1 mm of Hg. The reaction mixture was held at 290° C. and at a pressureof <1 mm of Hg until the power draw to the agitator no longer increased(70 minutes). The pressure of the pressure vessel was then increased to1 atmosphere using nitrogen gas. The molten polymer was then extrudedfrom the pressure vessel. The cooled, extruded polymer was ground topass a 6-mm screen. The polymer had an inherent viscosity of 0.736 dL/gand a Tg of 104° C. NMR analysis showed that the polymer was composed of85.4 mol % 1,4-cyclohexane-dimethanol residues and 14.6 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had colorvalues of: L*=78.20, a*=−1.62, and b*=6.23.

Example 3B to Example 3D

The polyesters described in Example 3B to Example 3D were preparedfollowing a procedure similar to the one described for Example 3A. Thecomposition and properties of these polyesters are shown in Table 3.

Example 3E

21.24 lb (49.71 gram-mol) dimethyl terephthalate, 12.61 lb (39.77gram-mol) 1,4-cyclohexanedimethanol, and 6.30 lb (19.88 gram-mol)2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted together in thepresence of 200 ppm of the catalyst butyltin tris(2-ethylhexanoate). Thereaction was carried out under a nitrogen gas purge in an 18-gallonstainless steel pressure vessel fitted with a condensing column, avacuum system, and a HELICONE-type agitator. With the agitator runningat 25 RPM, the reaction mixture temperature was increased to 250° C. andthe pressure was increased to 20 psig. The reaction mixture was held for2 hours at 250° C. and 20 psig pressure. The pressure was then decreasedto 0 psig at a rate of 3 psig/minute. The temperature of the reactionmixture was then increased to 270° C. and the pressure was decreased to90 mm of Hg. After a 1 hour hold time at 270° C. and 90 mm of Hg, theagitator speed was decreased to 15 RPM, the reaction mixture temperaturewas increased to 290° C., and the pressure was decreased to <1 mm of Hg.The reaction mixture was held at 290° C. and at a pressure of <1 mm ofHg for 60 minutes. The pressure of the pressure vessel was thenincreased to 1 atmosphere using nitrogen gas. The molten polymer wasthen extruded from the pressure vessel. The cooled, extruded polymer wasground to pass a 6-mm screen. The polymer had an inherent viscosity of0.715 dL/g and a Tg of 110° C. X-ray analysis showed that the polyesterhad 223 ppm tin. NMR analysis showed that the polymer was composed of78.6 mol % 1,4-cyclohexane-dimethanol residues and 21.4 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had colorvalues of: L*=76.45, a*=−1.65, and b*=6.47.

Example 3F

The polyester described in Example 3F was prepared following a proceduresimilar to the one described for Example 3A. The composition andproperties of this polyester are shown in Table 3.

Example 3H

21.24 lb (49.71 gram-mol) dimethyl terephthalate, 12.61 lb (39.77gram-mol) 1,4-cyclohexanedimethanol, and 6.30 lb (19.88 gram-mol)2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted together in thepresence of 200 ppm of the catalyst butyltin tris(2-ethylhexanoate). Thereaction was carried out under a nitrogen gas purge in an 18-gallonstainless steel pressure vessel fitted with a condensing column, avacuum system, and a HELICONE-type agitator. With the agitator runningat 25 RPM, the reaction mixture temperature was increased to 250° C. andthe pressure was increased to 20 psig. The reaction mixture was held for2 hours at 250° C. and 20 psig pressure. The pressure was then decreasedto 0 psig at a rate of 3 psig/minute. The temperature of the reactionmixture was then increased to 270° C. and the pressure was decreased to90 mm of Hg. After a 1 hour hold time at 270° C. and 90 mm of Hg, theagitator speed was decreased to 15 RPM, the reaction mixture temperaturewas increased to 290° C., and the pressure was decreased to <1 mm of Hg.The reaction mixture was held at 290° C. and at a pressure of <1 mm ofHg for 12 minutes. The pressure of the pressure vessel was thenincreased to 1 atmosphere using nitrogen gas. The molten polymer wasthen extruded from the pressure vessel. The cooled, extruded polymer wasground to pass a 6-mm screen. The polymer had an inherent viscosity of0.590 dL/g and a Tg of 106° C. NMR analysis showed that the polymer wascomposed of 77.1 mol % 1,4-cyclohexane-dimethanol residues and 22.9 mol% 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer hadcolor values of: L*=83.27, a*=−1.34, and b*=5.08.

Example 3I

21.24 lb (49.71 gram-mol) dimethyl terephthalate, 12.61 lb (39.77gram-mol) 1,4-cyclohexanedimethanol, and 6.30 lb (19.88 gram-mol)2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted together in thepresence of 200 ppm of the catalyst butyltin tris(2-ethylhexanoate). Thereaction was carried out under a nitrogen gas purge in an 18-gallonstainless steel pressure vessel fitted with a condensing column, avacuum system, and a HELICONE-type agitator. With the agitator runningat 25 RPM, the reaction mixture temperature was increased to 250° C. andthe pressure was increased to 20 psig. The reaction mixture was held for2 hours at 250° C. and 20 psig pressure. The pressure was then decreasedto 0 psig at a rate of 3 psig/minute. The temperature of the reactionmixture was then increased to 270° C. and the pressure was decreased to90 mm of Hg. After a 1 hour hold time at 270° C. and 90 mm of Hg, theagitator speed was decreased to 15 RPM, the reaction mixture temperaturewas increased to 290° C., and the pressure was decreased to 4 mm of Hg.The reaction mixture was held at 290° C. and at a pressure of 4 mm of Hgfor 30 minutes. The pressure of the pressure vessel was then increasedto 1 atmosphere using nitrogen gas. The molten polymer was then extrudedfrom the pressure vessel. The cooled, extruded polymer was ground topass a 6-mm screen. The polymer had an inherent viscosity of 0.531 dL/gand a Tg of 105° C. NMR analysis showed that the polymer was composed of76.9 mol % 1,4-cyclohexane-dimethanol residues and 23.1 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had colorvalues of: L*=80.42, a*=−1.28, and b*=5.13.

Example 3J

21.24 lb (49.71 gram-mol) dimethyl terephthalate, 12.61 lb (39.77gram-mol) 1,4-cyclohexanedimethanol, and 6.30 lb (19.88 gram-mol)2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted together in thepresence of 200 ppm of the catalyst butyltin tris(2-ethylhexanoate). Thereaction was carried out under a nitrogen gas purge in an 18-gallonstainless steel pressure vessel fitted with a condensing column, avacuum system, and a HELICONE-type agitator. With the agitator runningat 25 RPM, the reaction mixture temperature was increased to 250° C. andthe pressure was increased to 20 psig. The reaction mixture was held for2 hours at 250° C. and 20 psig pressure. The pressure was then decreasedto 0 psig at a rate of 3 psig/minute. The temperature of the reactionmixture was then increased to 270° C. and the pressure was decreased to90 mm of Hg. After a 1 hour hold time at 270° C. and 90 mm of Hg, theagitator speed was decreased to 15 RPM, the reaction mixture temperaturewas increased to 290° C., and the pressure was decreased to 4 mm of Hg.When the reaction mixture temperature was 290° C. and the pressure was 4mm of Hg, the pressure of the pressure vessel was immediately increasedto 1 atmosphere using nitrogen gas. The molten polymer was then extrudedfrom the pressure vessel. The cooled, extruded polymer was ground topass a 6-mm screen. The polymer had an inherent viscosity of 0.364 dL/gand a Tg of 98° C. NMR analysis showed that the polymer was composed of77.5 mol % 1,4-cyclohexane-dimethanol residues and 22.5 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had colorvalues of: L*=77.20, a*=−1.47, and b*=4.62.

Example 4

This example illustrates that 2,2,4,4-tetramethyl-1,3-cyclobutanediolcan improve the toughness of PCT-based copolyesters (polyesterscontaining terephthalic acid and 1,4-cyclohexanedimethanol). Polyestersprepared in this example fall comprise more than 25 to less than 40 mol% of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.

Copolyesters based on dimethyl terephthalate,2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 1,4-cyclohexanedimethanol(31/69 cis/trans) were prepared as described below, having thecomposition and properties shown on Table 4. The balance up to 100 mol %of the diol component of the polyesters in Table 4 was1,4-cyclohexanedimethanol (31/69 cis/trans).

Materials were injection molded into both 3.2 mm and 6.4 mm thick barsand subsequently notched for Izod impact testing. The notched Izodimpact strengths were obtained at 23° C. and are reported in Table 4.Density, Tg, and crystallization halftime were measured on the moldedbars. Melt viscosity was measured on pellets at 290° C. TABLE 4Compilation of various properties for certain polyesters useful in theinvention Notched Notched Izod of Izod of 3.2 mm 6.4 mm Melt thick thickCrystallization Viscosity Pellet Molded bars at bars at SpecificHalftime from at 1 rad/sec TMCD % cis IV Bar IV 23° C. 23° C. Gravity Tgmelt at 170° C. at 290° C. Example mole % TMCD (dl/g) (dl/g) (J/m) (J/m)(g/mL) (° C.) (min) (Poise) A 27 47.8 0.714 0.678 877 878 1.178 113 2808312 B 31 NA 0.667 0.641 807 789 1.174 116 600 6592NA = Not available.

Example 4A

21.24 lb (49.71 gram-mol) dimethyl terephthalate, 11.82 lb (37.28gram-mol) 1,4-cyclohexanedimethanol, and 6.90 lb (21.77 gram-mol)2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted together in thepresence of 200 ppm of the catalyst butyltin tris(2-ethylhexanoate). Thereaction was carried out under a nitrogen gas purge in an 18-gallonstainless steel pressure vessel fitted with a condensing column, avacuum system, and a HELICONE-type agitator. With the agitator runningat 25 RPM, the reaction mixture temperature was increased to 250° C. andthe pressure was increased to 20 psig. The reaction mixture was held for2 hours at 250° C. and 20 psig pressure. The pressure was then decreasedto 0 psig at a rate of 3 psig/minute. The temperature of the reactionmixture was then increased to 270° C. and the pressure was decreased to90 mm of Hg. After a 1 hour hold time at 270° C. and 90 mm of Hg, theagitator speed was decreased to 15 RPM, the reaction mixture temperaturewas increased to 290° C., and the pressure was decreased to <1 mm of Hg.The reaction mixture was held at 290° C. and at a pressure of <1 mm ofHg until the power draw to the agitator no longer increased (50minutes). The pressure of the pressure vessel was then increased to 1atmosphere using nitrogen gas. The molten polymer was then extruded fromthe pressure vessel. The cooled, extruded polymer was ground to pass a6-mm screen. The polymer had an inherent viscosity of 0.714 dL/g and aTg of 113° C. NMR analysis showed that the polymer was composed of 73.3mol % 1,4-cyclohexane-dimethanol residues and 26.7 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.

Example 4B

The polyester of Example 4B was prepared following a procedure similarto the one described for Example 4A. The composition and properties ofthis polyester are shown in Table 4.

Example 5

This example illustrates that 2,2,4,4-tetramethyl-1,3-cyclobutanediolcan improve the toughness of PCT-based copolyesters (polyesterscontaining terephthalic acid and 1,4-cyclohexanedimethanol). Polyestersprepared in this example comprise2,2,4,4-tetramethyl-1,3-cyclobutanediol residues in an amount of 40 mol% or greater.

Copolyesters based on dimethyl terephthalate,2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 1,4-cyclohexanedimethanolwere prepared as described below, having the composition and propertiesshown on Table 5. The balance up to 100 mol % of the diol component ofthe polyesters in Table 5 was 1,4-cyclohexanedimethanol (31/69cis/trans).

Materials were injection molded into both 3.2 mm and 6.4 mm thick barsand subsequently notched for Izod impact testing. The notched Izodimpact strengths were obtained at 23° C. and are reported in Table 5.Density, Tg, and crystallization halftime were measured on the moldedbars. Melt viscosity was measured on pellets at 290° C. TABLE 5Compilation of various properties for certain polyesters useful in theinvention Notched Notched Izod of Izod of 3.2 mm 6.4 mm Melt thick thickCrystallization Viscosity Pellet Molded bars at bars at SpecificHalftime from at 1 rad/sec TMCD % cis IV Bar IV 23° C. 23° C. Gravity Tgmelt at 170° C. at 290° C. Example mole % TMCD (dl/g) (dl/g) (J/m) (J/m)(g/mL) (° C.) (min) (Poise) A 44 46.2 0.657 0.626 727 734 1.172 119 NA9751 B 45 NA 0.626 0.580 748 237 1.167 123 NA 8051 C 45 NA 0.582 0.550671 262 1.167 125 19782 5835 D 45 NA 0.541 0.493 424 175 1.167 123 NA3275 E 59 46.6 0.604 0.576 456 311 1.156 139 NA 16537  F 45 47.2 0.4750.450 128  30 1.169 121 NA 1614NA = Not available.

Example 5A

21.24 lb (49.71 gram-mol) dimethyl terephthalate, 8.84 lb (27.88gram-mol) 1,4-cyclohexanedimethanol, and 10.08 lb (31.77 gram-mol)2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted together in thepresence of 200 ppm of the catalyst butyltin tris(2-ethylhexanoate). Thereaction was carried out under a nitrogen gas purge in an 18-gallonstainless steel pressure vessel fitted with a condensing column, avacuum system, and a HELICONE-type agitator. With the agitator runningat 25 RPM, the reaction mixture temperature was increased to 250° C. andthe pressure was increased to 20 psig. The reaction mixture was held for2 hours at 250° C. and 20 psig pressure. The pressure was then decreasedto 0 psig at a rate of 3 psig/minute. Then the agitator speed wasdecreased to 15 RPM, the temperature of the reaction mixture was thenincreased to 290° C. and the pressure was decreased to 2 mm of Hg. Thereaction mixture was held at 290° C. and at a pressure of 2 mm of Hguntil the power draw to the agitator no longer increased (80 minutes).The pressure of the pressure vessel was then increased to 1 atmosphereusing nitrogen gas. The molten polymer was then extruded from thepressure vessel. The cooled, extruded polymer was ground to pass a 6-mmscreen. The polymer had an inherent viscosity of 0.657 dL/g and a Tg of119° C. NMR analysis showed that the polymer was composed of 56.3 mol %1,4-cyclohexane-dimethanol residues and 43.7 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had colorvalues of: L*=75.04, a*=−1.82, and b*=6.72.

Example 5B to Example 5D

The polyesters described in Example 5B to Example 5D were preparedfollowing a procedure similar to the one described for Example 5A. Thecomposition and properties of these polyesters are shown in Table 5.

Example 5E

21.24 lb (49.71 gram-mol) dimethyl terephthalate, 6.43 lb (20.28gram-mol 1,4-cyclohexanedimethanol, and 12.49 lb (39.37 gram-mol)2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted together in thepresence of 200 ppm of the catalyst butyltin tris(2-ethylhexanoate). Thereaction was carried out under a nitrogen gas purge in an 18-gallonstainless steel pressure vessel fitted with a condensing column, avacuum system, and a HELICONE-type agitator. With the agitator runningat 25 RPM, the reaction mixture temperature was increased to 250° C. andthe pressure was increased to 20 psig. The reaction mixture was held for2 hours at 250° C. and 20 psig pressure. The pressure was then decreasedto 0 psig at a rate of 3 psig/minute. Then the agitator speed wasdecreased to 15 RPM, the temperature of the reaction mixture was thenincreased to 290° C. and the pressure was decreased to 2 mm of Hg. Thereaction mixture was held at 290° C. and at a pressure of <1 mm of Hguntil the power draw to the agitator no longer increased (50 minutes).The pressure of the pressure vessel was then increased to 1 atmosphereusing nitrogen gas. The molten polymer was then extruded from thepressure vessel. The cooled, extruded polymer was ground to pass a 6-mmscreen. The polymer had an inherent viscosity of 0.604 dL/g and a Tg of139° C. NMR analysis showed that the polymer was composed of 40.8 mol %1,4-cyclohexanedimethanol residues and 59.2 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. The polymer had colorvalues of: L*=80.48, a*=−1.30, and b*=6.82.

Example 5F

21.24 lb (49.71 gram-mol) dimethyl terephthalate, 8.84 lb (27.88gram-mol) 1,4-cyclohexanedimethanol, and 10.08 lb (31.77 gram-mol)2,2,4,4-tetramethyl-1,3-cyclobutanediol were reacted together in thepresence of 200 ppm of the catalyst butyltin tris(2-ethylhexanoate). Thereaction was carried out under a nitrogen gas purge in an 18-gallonstainless steel pressure vessel fitted with a condensing column, avacuum system, and a HELICONE-type agitator. With the agitator runningat 25 RPM, the reaction mixture temperature was increased to 250° C. andthe pressure was increased to 20 psig. The reaction mixture was held for2 hours at 250° C. and 20 psig pressure. The pressure was then decreasedto 0 psig at a rate of 3 psig/minute. The temperature of the reactionmixture was then increased to 270° C. and the pressure was decreased to90 mm of Hg. After a 1 hour hold time at 270° C. and 90 mm of Hg, theagitator speed was decreased to 15 RPM and the pressure was decreased to4 mm of Hg. When the reaction mixture temperature was 270° C. and thepressure was 4 mm of Hg, the pressure of the pressure vessel wasimmediately increased to 1 atmosphere using nitrogen gas. The moltenpolymer was then extruded from the pressure vessel. The cooled, extrudedpolymer was ground to pass a 6-mm screen. The polymer had an inherentviscosity of 0.475 dL/g and a Tg of 121° C. NMR analysis showed that thepolymer was composed of 55.5 mol % 1,4-cyclohexane-dimethanol residuesand 44.5 mol % 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues. Thepolymer had color values of: L*=85.63, a*=−0.88, and b*=4.34.

Example 6—Comparative Example

This example shows data for comparative materials are shown in Table 6.The PC was Makrolon 2608 from Bayer, with a nominal composition of 100mole % bisphenol A residues and 100 mole % diphenyl carbonate residues.Makrolon 2608 has a nominal melt flow rate of 20 grams/10 minutesmeasured at 300 C using a 1.2 kg weight. The PET was Eastar 9921 fromEastman Chemical Company, with a nominal composition of 100 mole %terephthalic acid, 3.5 mole % cyclohexanedimethanol (CHDM) and 96.5 mole% ethylene glycol. The PETG was Eastar 6763 from Eastman ChemicalCompany, with a nominal composition of 100 mole % terephthalic acid, 31mole % cyclohexanedimethanol (CHDM) and 69 mole % ethylene glycol. ThePCTG was Eastar DN001 from Eastman Chemical Company, with a nominalcomposition of 100 mole % terephthalic acid, 62 mole %cyclohexanedimethanol (CHDM) and 38 mole % ethylene glycol. The PCTA wasEastar AN001 from Eastman Chemical Company, with a nominal compositionof 65 mole % terephthalic acid, 35 mole % isophthalic acid and 100 mole% cyclohexanedimethanol (CHDM). The Polysulfone was Udel 1700 fromSolvay, with a nominal composition of 100 mole % bisphenol A residuesand 100 mole % 4,4-dichlorosulfonyl sulfone residues. Udel 1700 has anominal melt flow rate of 6.5 grams/10 minutes measured at 343 C using a2.16 kg weight. The SAN was Lustran 31 from Lanxess, with a nominalcomposition of 76 weight % styrene and 24 weight % acrylonitrile.Lustran 31 has a nominal melt flow rate of 7.5 grams/10 minutes measuredat 230 C using a 3.8 kg weight. The examples of the invention showimproved toughness in 6.4 mm thickness bars compared to all of the otherresins. TABLE 6 Compilation of various properties for certain commercialpolymers Notched Notched Izod of Izod of 3.2 mm 6.4 mm thick thickCrystallization Pellet Molded bars at bars at Specific Halftime fromPolymer IV Bar IV 23° C. 23° C. Gravity Tg melt Example name (dl/g)(dl/g) (J/m) (J/m) (g/mL) (° C.) (min) A PC  12 MFR NA 929  108  1.20146 NA B PCTG 0.73 0.696 NB 70 1.23 87 30 at 170° C. C PCTA 0.72 0.70298 59 1.20 87 15 at 150° C. D PETG 0.75 0.692 83 59 1.27 80 2500 at 130°C.  E PET 0.76 0.726 45 48 1.33 78 1.5 at 170° C.  F SAN 7.5 MFR NA 21NA 1.07 ˜110 NA G PSU 6.5 MFR NA 69 NA 1.24 ˜190 NANA = Not available

Example 7

This example illustrates the effect of the amount of2,2,4,4-tetramethyl-1,3-cyclobutanediol used for the preparation of thepolyesters of the invention on the glass transition temperature of thepolyesters. Polyesters prepared in this example comprise from 15 to 25mol % of 2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.

Example 7A to Example 7G

Dimethyl terephthalate, 1,4-cyclohexanedimethanol, and2,2,4,4-tetramethyl-1,3-cyclobutanediol were weighed into a 500-mlsingle neck round bottom flask. NMR analysis on the2,2,4,4-tetramethyl-1,3-cyclobutanediol starting material showed acis/trans ratio of 53/47. The polyesters of this example were preparedwith a 1.2/1 glycol/acid ratio with the entire excess coming from the2,2,4,4-tetramethyl-1,3-cyclobutanediol. Enough dibutyltin oxidecatalyst was added to give 300 ppm tin in the final polymer. The flaskwas under a 0.2 SCFC nitrogen purge with vacuum reduction capability.The flask was immersed in a Belmont metal bath at 200° C. and stirred at200 RPM after the reactants had melted. After about 2.5 hours, thetemperature was raised to 210° C. and these conditions were held for anadditional 2 hours. The temperature was raised to 285° C. (inapproximately 25 minutes) and the pressure was reduced to 0.3 mm of Hgover a period of 5 minutes. The stirring was reduced as the viscosityincreased, with 15 RPM being the minimum stirring used. The totalpolymerization time was varied to attain the target inherentviscosities. After the polymerization was complete, the Belmont metalbath was lowered and the polymer was allowed to cool to below its glasstransition temperature. After about 30 minutes, the flask was reimmersedin the Belmont metal bath (the temperature had been increased to 295° C.during this 30 minute wait) and the polymer mass was heated until itpulled away from the glass flask. The polymer mass was stirred at midlevel in the flask until the polymer had cooled. The polymer was removedfrom the flask and ground to pass a 3 mm screen. Variations to thisprocedure were made to produce the copolyesters described below with atargeted composition of 20 mol %.

Inherent viscosities were measured as described in the “MeasurementMethods” section above. The compositions of the polyesters weredetermined by ¹H NMR as explained before in the Measurement Methodssection. The glass transition temperatures were determined by DSC, usingthe second heat after quench at a rate of 20° C./min.

Example 7H to Example 7Q

These polyesters were prepared by carrying out the ester exchange andpolycondensation reactions in separate stages. The ester exchangeexperiments were conducted in a continuous temperature rise (CTR)reactor. The CTR was a 3000 ml glass reactor equipped with a singleshaft impeller blade agitator, covered with an electric heating mantleand fitted with a heated packed reflux condenser column. The reactor wascharged with 777 g (4 moles) of dimethyl terephthalate, 230 g (1.6moles) of 2,2,4,4-tetramethyl-1,3-cyclobutanediol, 460.8 g (3.2 moles)of cyclohexanedimethanol and 1.12 g of butyltin tris-2-ethylhexanoate(such that there will be 200 ppm tin metal in the final polymer). Theheating mantle was set manually to 100% output. The set points and datacollection were facilitated by a Camile process control system. Once thereactants were melted, stirring was initiated and slowly increased to250 rpm. The temperature of the reactor gradually increased with runtime. The weight of methanol collected was recorded via balance. Thereaction was stopped when methanol evolution stopped or at apre-selected lower temperature of 260° C. The oligomer was dischargedwith a nitrogen purge and cooled to room temperature. The oligomer wasfrozen with liquid nitrogen and broken into pieces small enough to beweighed into a 500 ml round bottom flask.

In the polycondensation reactions, a 500 ml round bottom flask wascharged with approximately 150 g of the oligomer prepared above. Theflask was equipped with a stainless steel stirrer and polymer head. Theglassware was set up on a half mole polymer rig and the Camile sequencewas initiated. The stirrer was positioned one full turn from the flaskbottom once the oligomer melted. The temperature/pressure/stir ratesequence controlled by the Camile software for each example is reportedin the following tables.

Camile Sequence for Example 7 H and Example 7I Time Vacuum Stir Stage(min) Temp (° C.) (torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 76050 4 3 265 90 50 5 110 290 90 50 6 5 290 6 25 7 110 290 6 25

Camile Sequence for Example 7N to Example 7Q Time Vacuum Stir Stage(min) Temp (° C.) (torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 76050 4 3 265 90 50 5 110 290 90 50 6 5 290 3 25 7 110 290 3 25

Camile Sequence for Example 7K and Example 7L Time Vacuum Stir Stage(min) Temp (° C.) (torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 76050 4 3 265 90 50 5 110 290 90 50 6 5 290 2 25 7 110 290 2 25

Camile Sequence for Example 7J and Example 7M Time Vacuum Stir Stage(min) Temp (° C.) (torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 76050 4 3 265 90 50 5 110 290 90 50 6 5 290 1 25 7 110 290 1 25

The resulting polymers were recovered from the flask, chopped using ahydraulic chopper, and ground to a 6 mm screen size. Samples of eachground polymer were submitted for inherent viscosity in 60/40 (wt/wt)phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at 25° C.,catalyst level (Sn) by x-ray fluorescence, and color (L*, a*, b*) bytransmission spectroscopy. Polymer composition was obtained by ¹H NMR.Samples were submitted for thermal stability and melt viscosity testingusing a Rheometrics Mechanical Spectrometer (RMS-800).

The table below shows the experimental data for the polyesters of thisexample. The data shows that an increase in the level of2,2,4,4-tetramethyl-1,3-cyclobutanediol raises the glass transitiontemperature in an almost linear fashion, for a constant inherentviscosity. FIG. 3 also shows the dependence of Tg on composition andinherent viscosity. TABLE 7 Glass transition temperature as a functionof inherent viscosity and composition % cis η_(o) at 260° C. η_(o) at275° C. η_(o) at 290° C. Example mol % TMCD TMCD IV (dL/g) T_(g) (° C.)(Poise) (Poise) (Poise) A 20 51.4 0.72 109 11356 19503 5527 B 19.1 51.40.60 106 6891 3937 2051 C 19 53.2 0.64 107 8072 4745 2686 D 18.8 54.40.70 108 14937 8774 4610 E 17.8 52.4 0.50 103 3563 1225 883 F 17.5 51.90.75 107 21160 10877 5256 G 17.5 52 0.42 98 NA NA NA H 22.8 53.5 0.69109 NA NA NA I 22.7 52.2 0.68 108 NA NA NA J 23.4 52.4 0.73 111 NA NA NAK 23.3 52.9 0.71 111 NA NA NA L 23.3 52.4 0.74 112 NA NA NA M 23.2 52.50.74 112 NA NA NA N 23.1 52.5 0.71 111 NA NA NA O 22.8 52.4 0.73 112 NANA NA P 22.7 53 0.69 112 NA NA NA Q 22.7 52 0.70 111 NA NA NANA = Not available

Example 8

This example illustrates the effect of the amount of2,2,4,4-tetramethyl-1,3-cyclobutanediol used for the preparation of thepolyesters of the invention on the glass transition temperature of thepolyesters. Polyesters prepared in this example fall comprise more than25 to less than 40 mol % of 2,2,4,4-tetramethyl-1,3-cyclobutanediolresidues.

Dimethyl terephthalate, 1,4-cyclohexanedimethanol, and2,2,4,4-tetramethyl-1,3-cyclobutanediol were weighed into a 500-mlsingle neck round bottom flask. NMR analysis on the2,2,4,4-tetramethyl-1,3-cyclobutanediol starting material showed acis/trans ratio of 53/47. The polyesters of this example were preparedwith a 1.2/1 glycol/acid ratio with the entire excess coming from the2,2,4,4-tetramethyl-1,3-cyclobutanediol. Enough dibutyltin oxidecatalyst was added to give 300 ppm tin in the final polymer. The flaskwas under a 0.2 SCFC nitrogen purge with vacuum reduction capability.The flask was immersed in a Belmont metal bath at 200° C. and stirred at200 RPM after the reactants had melted. After about 2.5 hours, thetemperature was raised to 210° C. and these conditions were held for anadditional 2 hours. The temperature was raised to 285° C. (inapproximately 25 minutes) and the pressure was reduced to 0.3 mm of Hgover a period of 5 minutes. The stirring was reduced as the viscosityincreased, with 15 RPM being the minimum stirring used. The totalpolymerization time was varied to attain the target inherentviscosities. After the polymerization was complete, the Belmont metalbath was lowered and the polymer was allowed to cool to below its glasstransition temperature. After about 30 minutes, the flask was reimmersedin the Belmont metal bath (the temperature had been increased to 295° C.during this 30 minute wait) and the polymer mass was heated until itpulled away from the glass flask. The polymer mass was stirred at midlevel in the flask until the polymer had cooled. The polymer was removedfrom the flask and ground to pass a 3 mm screen. Variations to thisprocedure were made to produce the copolyesters described below with atargeted composition of 32 mol %.

Inherent viscosities were measured as described in the “MeasurementMethods” section above. The compositions of the polyesters weredetermined by ¹H NMR as explained before in the Measurement Methodssection. The glass transition temperatures were determined by DSC, usingthe second heat after quench at a rate of 20° C./min.

The table below shows the experimental data for the polyesters of thisexample. FIG. 3 also shows the dependence of Tg on composition andinherent viscosity. The data shows that an increase in the level of2,2,4,4-tetramethyl-1,3-cyclobutanediol raises the glass transitiontemperature in an almost linear fashion, for a constant inherentviscosity. TABLE 8 Glass transition temperature as a function ofinherent viscosity and composition η_(o) at % cis η_(o) at 260° C. 275°C. η_(o) at 290° C. Example mol % TMCD TMCD IV (dL/g) T_(g) (° C.)(Poise) (Poise) (Poise) A 32.2 51.9 0.71 118 29685 16074 8522 B 31.651.5 0.55 112 5195 2899 2088 C 31.5 50.8 0.62 112 8192 4133 2258 D 30.750.7 0.54 111 4345 2434 1154 E 30.3 51.2 0.61 111 7929 4383 2261 F 30.051.4 0.74 117 31476 17864 8630 G 29.0 51.5 0.67 112 16322 8787 4355 H31.1 51.4 0.35 102 NA NA NANA = Not available

Example 9

This example illustrates the effect of the amount of2,2,4,4-tetramethyl-1,3-cyclobutanediol used for the preparation of thepolyesters of the invention on the glass transition temperature of thepolyesters. Polyesters prepared in this example comprise2,2,4,4-tetramethyl-1,3-cyclobutanediol residues in an amount of 40 mol% or greater.

Examples A to AC

These polyesters were prepared by carrying out the ester exchange andpolycondensation reactions in separate stages. The ester exchangeexperiments were conducted in a continuous temperature rise (CTR)reactor. The CTR was a 3000 ml glass reactor equipped with a singleshaft impeller blade agitator, covered with an electric heating mantleand fitted with a heated packed reflux condenser column. The reactor wascharged with 777 g of dimethyl terephthalate, 375 g of2,2,4,4-tetramethyl-1,3-cyclobutanediol, 317 g of cyclohexanedimethanoland 1.12 g of butyltin tris-2-ethylhexanoate (such that there will be200 ppm tin metal in the final polymer). The heating mantle was setmanually to 100% output. The set points and data collection werefacilitated by a Camile process control system. Once the reactants weremelted, stirring was initiated and slowly increased to 250 rpm. Thetemperature of the reactor gradually increased with run time. The weightof methanol collected was recorded via balance. The reaction was stoppedwhen methanol evolution stopped or at a pre-selected lower temperatureof 260° C. The oligomer was discharged with a nitrogen purge and cooledto room temperature. The oligomer was frozen with liquid nitrogen andbroken into pieces small enough to be weighed into a 500 ml round bottomflask.

In the polycondensation reactions, a 500 ml round bottom flask wascharged with 150 g of the oligomer prepared above. The flask wasequipped with a stainless steel stirrer and polymer head. The glasswarewas set up on a half mole polymer rig and the Camile sequence wasinitiated. The stirrer was positioned one full turn from the flaskbottom once the oligomer melted. The temperature/pressure/stir ratesequence controlled by the Camile software for these examples isreported in the following table, unless otherwise specified below.Camile Sequence for Polycondensation Reactions Time Vacuum Stir Stage(min) Temp (° C.) (torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 76050 4 3 265 90 50 5 110 290 90 50 6 5 290 6 25 7 110 290 6 25

Camile Sequence for Examples A, C, R, Y, AB, AC Time Vacuum Stir Stage(min) Temp (° C.) (torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 76050 4 3 265 90 50 5 110 290 90 50 6 5 290 6 25 7 110 290 6 25

For Examples B, D, F, the same sequence in the preceding table was used,except the time was 80 min in Stage 7. For Examples G and J, the samesequence in the preceding table was used, except the time was 50 min inStage 7. For Example L, the same sequence in the preceding table wasused, except the time was 140 min in Stage 7.

Camile Sequence for Example E Time Vacuum Stir Stage (min) Temp (° C.)(torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265 90 505 110 300 90 50 6 5 300 7 25 7 110 300 7 25

For Example I, the same sequence in the preceding table was used, exceptthe vacuum was 8 torr in Stages 6 and 7. For Example O, the samesequence in the preceding table was used, except the vacuum was 6 torrin Stages 6 and 7. For Example P, the same sequence in the precedingtable was used, except the vacuum was 4 torr in Stages 6 and 7. ForExample Q, the same sequence in the preceding table was used, except thevacuum was 5 torr in Stages 6 and 7.

Camile Sequence for Example H Time Vacuum Stir Stage (min) Temp (° C.)(torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265 90 505 110 280 90 50 6 5 280 5 25 7 110 280 5 25

For Example U and AA, the same sequence in the preceding table was used,except the vacuum was 6 torr in Stages 6 and 7. For Example V and X, thesame sequence in the preceding table was used, except the vacuum was 6torr and stir rate was 15 rpm in Stages 6 and 7. For Example Z, the samesequence in the preceding table was used, except the stir rate was 15rpm in Stages 6 and 7.

Camile Sequence for Example K Time Vacuum Stir Stage (min) Temp (° C.)(torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265 90 505 110 300 90 50 6 5 300 6 15 7 110 300 6 15

For Example M, the same sequence in the preceding table was used, exceptthe vacuum was 8 torr in Stages 6 and 7. For Example N, the samesequence in the preceding table was used, except the vacuum was 7 torrin Stages 6 and 7.

Camile Sequence for Examples S and T Time Temp Vacuum Stir Stage (min)(° C.) (torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 760 50 4 5 2906 25 5 110 290 6 25

The resulting polymers were recovered from the flask, chopped using ahydraulic chopper, and ground to a 6 mm screen size. Samples of eachground polymer were submitted for inherent viscosity in 60/40 (wt/wt)phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at 25° C.,catalyst level (Sn) by x-ray fluorescence, and color (L*, a*, b*) bytransmission spectroscopy. Polymer composition was obtained by 1H NMR.Samples were submitted for thermal stability and melt viscosity testingusing a Rheometrics Mechanical Spectrometer (RMS-800).

Examples AD to AK and AT

The polyesters of these examples were prepared as described above forExamples A to AC, except that the target tin amount in the final polymerwas 150 ppm for examples AD to AK and AT. The following tables describethe temperature/pressure/stir rate sequences controlled by the Camilesoftware for these examples.

Camile Sequence for Examples AD, AF, and AH Time Temp Vacuum Stir Stage(min) (° C.) (torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 760 50 43 265 400 50 5 110 290 400 50 6 5 290 8 50 7 110 295 8 50

For Example AD, the stirrer was turned to 25 rpm with 95 min left inStage 7.

Camile Sequence for Example AE Time Temp Vacuum Stir Stage (min) (° C.)(torr) (rpm) 1 10 245 760 0 2 5 245 760 50 3 30 283 760 50 4 3 283 17550 5 5 283 5 50 6 5 283 1.2 50 7 71 285 1.2 50

For Example AK, the same sequence in the preceding table was used,excepts the time was 75 min in Stage 7.

Camile Sequence for Example AG Time Temp Vacuum Stir Stage (min) (° C.)(torr) (rpm) 1 10 245 760 0 2 5 245 760 50 3 30 285 760 50 4 3 285 17550 5 5 285 5 50 6 5 285 4 50 7 220 290 4 50

Camile Sequence for Example AI Time Temp Vacuum Stir Stage (min) (° C.)(torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265 90 505 110 285 90 50 6 5 285 6 50 7 70 290 6 50

Camile Sequence for Example AJ Time Temp Vacuum Stir Stage (min) (° C.)(torr) (rpm) 1 5 245 760 0 2 5 245 760 50 3 30 265 760 50 4 3 265 90 505 110 290 90 50 6 5 290 6 25 7 110 295 6 25

Example AL to AS

Dimethyl terephthalate, 1,4-cyclohexanedimethanol, and2,2,4,4-tetramethyl-1,3-cyclobutanediol were weighed into a 500-mlsingle neck round bottom flask. The polyesters of this example wereprepared with a 1.2/1 glycol/acid ratio with the entire excess comingfrom the 2,2,4,4-tetramethyl-1,3-cyclobutanediol. Enough dibutyltinoxide catalyst was added to give 300 ppm tin in the final polymer. Theflask was under a 0.2 SCFC nitrogen purge with vacuum reductioncapability. The flask was immersed in a Belmont metal bath at 200° C.and stirred at 200 RPM after the reactants had melted. After about 2.5hours, the temperature was raised to 210° C. and these conditions wereheld for an additional 2 hours. The temperature was raised to 285° C.(in approximately 25 minutes) and the pressure was reduced to 0.3 mm ofHg over a period of 5 minutes. The stirring was reduced as the viscosityincreased, with 15 RPM being the minimum stirring used. The totalpolymerization time was varied to attain the target inherentviscosities. After the polymerization was complete, the Belmont metalbath was lowered and the polymer was allowed to cool to below its glasstransition temperature. After about 30 minutes, the flask was reimmersedin the Belmont metal bath (the temperature had been increased to 295° C.during this 30 minute wait) and the polymer mass was heated until itpulled away from the glass flask. The polymer mass was stirred at midlevel in the flask until the polymer had cooled. The polymer was removedfrom the flask and ground to pass a 3 mm screen. Variations to thisprocedure were made to produce the copolyesters described below with atargeted composition of 45 mol %.

Inherent viscosities were measured as described in the “MeasurementMethods” section above. The compositions of the polyesters weredetermined by ¹H NMR as explained before in the Measurement Methodssection. The glass transition temperatures were determined by DSC, usingthe second heat after quench at a rate of 20° C./min.

The table below shows the experimental data for the polyesters of thisexample. The data shows that an increase in the level of2,2,4,4-tetramethyl-1,3-cyclobutanediol raises the glass transitiontemperature in an almost linear fashion, for a constant inherentviscosity. FIG. 3 also shows the dependence of Tg on composition andinherent viscosity. TABLE 9 Glass transition temperature as a functionof inherent viscosity and composition η_(o) at η_(o) at η_(o) at Ex- mol% % cis IV T_(g) 260° C. 275° C. 290° C. ample TMCD TMCD (dL/g) (° C.)(Poise) (Poise) (Poise) A 43.9 72.1 0.46 131 NA NA NA B 44.2 36.4 0.49118 NA NA NA C 44 71.7 0.49 128 NA NA NA D 44.3 36.3 0.51 119 NA NA NA E46.1 46.8 0.51 125 NA NA NA F 43.6 72.1 0.52 128 NA NA NA G 43.6 72.30.54 127 NA NA NA H 46.4 46.4 0.54 127 NA NA NA I 45.7 47.1 0.55 125 NANA NA J 44.4 35.6 0.55 118 NA NA NA K 45.2 46.8 0.56 124 NA NA NA L 43.872.2 0.56 129 NA NA NA M 45.8 46.4 0.56 124 NA NA NA N 45.1 47.0 0.57125 NA NA NA O 45.2 46.8 0.57 124 NA NA NA P 45 46.7 0.57 125 NA NA NA Q45.1 47.1 0.58 127 NA NA NA R 44.7 35.4 0.59 123 NA NA NA S 46.1 46.40.60 127 NA NA NA T 45.7 46.8 0.60 129 NA NA NA U 46 46.3 0.62 128 NA NANA V 45.9 46.3 0.62 128 NA NA NA X 45.8 46.1 0.63 128 NA NA NA Y 45.650.7 0.63 128 NA NA NA Z 46.2 46.8 0.65 129 NA NA NA AA 45.9 46.2 0.66128 NA NA NA AB 45.2 46.4 0.66 128 NA NA NA AC 45.1 46.5 0.68 129 NA NANA AD 46.3 52.4 0.52 NA NA NA NA AE 45.7 50.9 0.54 NA NA NA NA AF 46.352.6 0.56 NA NA NA NA AG 46 50.6 0.56 NA NA NA NA AH 46.5 51.8 0.57 NANA NA NA AI 45.6 51.2 0.58 NA NA NA NA AJ 46 51.9 0.58 NA NA NA NA AK45.5 51.2 0.59 NA NA NA NA AL 45.8 50.1 0.624 125 NA NA 7696 AM 45.749.4 0.619 128 NA NA 7209 AN 46.2 49.3 0.548 124 NA NA 2348 AP 45.9 49.50.72 128 76600 40260 19110  AQ 46.0 50 0.71 131 68310 32480 17817  AR46.1 49.6 0.383 117 NA NA  387 AS 45.6 50.5 0.325 108 NA NA NA AT 47.2NA 0.48 NA NA NA NANA = Not available

Example 10

This example illustrates the effect of the predominance of the type of2,2,4,4-tetramethyl-1,3-cyclobutanediol isomer (cis or trans) on theglass transition temperature of the polyester.

Dimethyl terephthalate, 1,4-cyclohexanedimethanol, and2,2,4,4-tetramethyl-1,3-cyclobutanediol were weighed into a 500-mlsingle neck round bottom flask. The polyesters of this example wereprepared with a 1.2/1 glycol/acid ratio with the entire excess comingfrom the 2,2,4,4-tetramethyl-1,3-cyclobutanediol. Enough dibutyltinoxide catalyst was added to give 300 ppm tin in the final polymer. Theflask was under a 0.2 SCFC nitrogen purge with vacuum reductioncapability. The flask was immersed in a Belmont metal bath at 200° C.and stirred at 200 RPM after the reactants had melted. After about 2.5hours, the temperature was raised to 210° C. and these conditions wereheld for an additional 2 hours. The temperature was raised to 285° C.(in approximately 25 minutes) and the pressure was reduced to 0.3 mm ofHg over a period of 5 minutes. The stirring was reduced as the viscosityincreased, with 15 RPM being the minimum stirring used. The totalpolymerization time was varied to attain the target inherentviscosities. After the polymerization was complete, the Belmont metalbath was lowered and the polymer was allowed to cool to below its glasstransition temperature. After about 30 minutes, the flask was reimmersedin the Belmont metal bath (the temperature had been increased to 295° C.during this 30 minute wait) and the polymer mass was heated until itpulled away from the glass flask. The polymer mass was stirred at midlevel in the flask until the polymer had cooled. The polymer was removedfrom the flask and ground to pass a 3 mm screen. Variations to thisprocedure were made to produce the copolyesters described below with atargeted composition of 45 mol %.

Inherent viscosities were measured as described in the “MeasurementMethods” section above. The compositions of the polyesters weredetermined by ¹H NMR as explained before in the Measurement Methodssection. The glass transition temperatures were determined by DSC, usingthe second heat after quench at a rate of 20° C./min.

The table below shows the experimental data for the polyesters of thisExample. The data shows that cis 2,2,4,4-tetramethyl-1,3-cyclobutanediolis approximately twice as effective as trans2,2,4,4-tetramethyl-1,3-cyclobutanediol at increasing the glasstransition temperature for a constant inherent viscosity. TABLE 10Effect of 2,2,4,4-tetramethyl-1,3-cyclobutanediol cis/trans compositionon T_(g) η_(o) at η_(o) at η_(o) at Ex- mol % IV T_(g) 260° C. 275° C.290° C. % cis ample TMCD (dL/g) (° C.) (Poise) (Poise) (Poise) TMCD A45.8 0.71 119 N.A. N.A. N.A. 4.1 B 43.2 0.72 122 N.A. N.A. N.A. 22.0 C46.8 0.57 119 26306 16941 6601 22.8 D 43.0 0.67 125 55060 36747 1441023.8 E 43.8 0.72 127 101000 62750 25330 24.5 F 45.9 0.533 119 11474 68642806 26.4 G 45.0 0.35 107 N.A. N.A. N.A. 27.2 H 41.2 0.38 106 1214 757N.A. 29.0 I 44.7 0.59 123 N.A. N.A. N.A. 35.4 J 44.4 0.55 118 N.A. N.A.N.A. 35.6 K 44.3 0.51 119 N.A. N.A. N.A. 36.3 L 44.0 0.49 128 N.A. N.A.N.A. 71.7 M 43.6 0.52 128 N.A. N.A. N.A. 72.1 N 43.6 0.54 127 N.A. N.A.N.A. 72.3 O 41.5 0.58 133 15419 10253 4252 88.7 P 43.8 0.57 135 1621910226 4235 89.6 Q 41.0 0.33 120 521 351 2261 90.4 R 43.0 0.56 134 N.A.NA. N.A. 90.6 S 43.0 0.49 132 7055 4620 2120 90.6 T 43.1 0.55 134 129708443 3531 91.2 U 45.9 0.52 137 N.A. N.A. N.A. 98.1NA = not available

Example 11

This example illustrates the preparation of a copolyester containing 100mol % dimethyl terephthalate residues, 55 mol %1,4-cyclohexanedimethanol residues, and 45 mol %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues.

A mixture of 97.10 g (0.5 mol) dimethyl terephthalate, 52.46 g (0.36mol) 1,4-cyclohexanedimethanol, 34.07 g (0.24 mol)2,2,4,4-tetramethyl-1,3-cyclobutanediol, and 0.0863 g (300 ppm) dibutyltin oxide was placed in a 500-milliliter flask equipped with an inletfor nitrogen, a metal stirrer, and a short distillation column. Theflask was placed in a Wood's metal bath already heated to 200° C. Thecontents of the flask were heated at 200° C. for 1 hour and then thetemperature was increased to 210° C. The reaction mixture was held at210° C. for 2 hours and then heated up to 290° C. in 30 minutes. Once at290° C., a vacuum of 0.01 psig was gradually applied over the next 3 to5 minutes. Full vacuum (0.01 psig) was maintained for a total time ofabout 45 minutes to remove excess unreacted diols. A high meltviscosity, visually clear and colorless polymer was obtained with aglass transition temperature of 125° C. and an inherent viscosity of0.64 dL/g.

Example 12—Comparative Example

This example illustrates that a polyester based on 100%2,2,4,4-tetramethyl-1,3-cyclobutanediol has a slow crystallizationhalf-time.

A polyester based solely on terephthalic acid and2,2,4,4-tetramethyl-1,3-cyclobutanediol was prepared in a method similarto the method described in Example 1A with the properties shown on Table11. This polyester was made with 300 ppm dibutyl tin oxide. Thetrans/cis ratio of the 2,2,4,4-tetramethyl-1,3-cyclobutanediol was65/35.

Films were pressed from the ground polymer at 320° C. Crystallizationhalf-time measurements from the melt were made at temperatures from 220to 250° C. at 10° C. increments and are reported in Table 11. Thefastest crystallization half-time for the sample was taken as theminimum value of crystallization half-time as a function of temperature.The fastest crystallization half-time of this polyester is around 1300minutes. This value contrasts with the fact that the polyester (PCT)based solely on terephthalic acid and 1,4-cyclohexanedimethanol (nocomonomer modification) has an extremely short crystallization half-time(<1 min) as shown in FIG. 1. TABLE 11 Crystallization Half-times (min)at at at at Comonomer IV T_(g) T_(max) 220° C. 230° C. 240° C. 250° C.(mol %) (dl/g) (° C.) (° C.) (min) (min) (min) (min) 100 mol % F 0.63170.0 330 3291 3066 1303 1888where:F is 2,2,4,4-Tetramethyl-1,3-cyclobutanediol (65/35 Trans/Cis)

Example 13

Sheets comprising a polyester that had been prepared with a targetcomposition of 100 mole % terephthalic acid residues, 80 mole %1,4-cyclohexanedimethanol residues, and 20 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues were produced using a3.5 inch single screw extruder. A sheet was extruded continuously,gauged to a thickness of 177 mil and then various sheets were sheared tosize. Inherent viscosity and glass transition temperature were measuredon one sheet. The sheet inherent viscosity was measured to be 0.69 dL/g.The glass transition temperature of the sheet was measured to be 106° C.Sheets were then conditioned at 50% relative humidity and 60° C. for 2weeks. Sheets were subsequently thermoformed into a female mold having adraw ratio of 2.5:1 using a Brown thermoforming machine. Thethermoforming oven heaters were set to 70/60/60% output using top heatonly. Sheets were left in the oven for various amounts of time in orderto determine the effect of sheet temperature on the part quality asshown in the table below. Part quality was determined by measuring thevolume of the thermoformed part, calculating the draw, and visuallyinspecting the thermoformed part. The draw was calculated as the partvolume divided by the maximum part volume achieved in this set ofexperiments (Example G). The thermoformed part was visually inspectedfor any blisters and the degree of blistering rated as none (N), low(L), or high (H). The results below demonstrate that these thermoplasticsheets with a glass transition temperature of 106° C. can bethermoformed under the conditions shown below, as evidenced by thesesheets having at least 95% draw and no blistering, without predrying thesheets prior to thermoforming. Thermoforming Conditions Part QualitySheet Part Heat Time Temperature Volume Blisters Example (s) (° C.) (mL)Draw (%) (N, L, H) A 86 145 501 64 N B 100 150 500 63 N C 118 156 672 85N D 135 163 736 94 N E 143 166 760 97 N F 150 168 740 94 L G 159 172 787100 L

Example 14

Sheets comprising a polyester that had been prepared with a targetcomposition of 100 mole % terephthalic acid residues, 80 mole %1,4-cyclohexanedimethanol residues, and 20 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol residues were produced using a3.5 inch single screw. A sheet was extruded continuously, gauged to athickness of 177 mil and then various sheets were sheared to size.Inherent viscosity and glass transition temperature were measured on onesheet. The sheet inherent viscosity was measured to be 0.69 dL/g. Theglass transition temperature of the sheet was measured to be 106° C.Sheets were then conditioned at 100% relative humidity and 25° C. for 2weeks. Sheets were subsequently thermoformed into a female mold having adraw ratio of 2.5:1 using a Brown thermoforming machine. Thethermoforming oven heaters were set to 60/40/40% output using top heatonly. Sheets were left in the oven for various amounts of time in orderto determine the effect of sheet temperature on the part quality asshown in the table below. Part quality was determined by measuring thevolume of the thermoformed part, calculating the draw, and visuallyinspecting the thermoformed part. The draw was calculated as the partvolume divided by the maximum part volume achieved in this set ofexperiments (Example G). The thermoformed part was visually inspectedfor any blisters and the degree of blistering rated as none (N), low(L), or high (H). The results below demonstrate that these thermoplasticsheets with a glass transition temperature of 106° C. can bethermoformed under the conditions shown below, as evidenced by theproduction of sheets having at least 95% draw and no blistering, withoutpredrying the sheets prior to thermoforming. Thermoforming ConditionsPart Quality Sheet Part Heat Time Temperature Volume Blisters Example(s) (° C.) (mL) Draw (%) (N, L, H) A 141 154 394 53 N B 163 157 606 82 NC 185 160 702 95 N D 195 161 698 95 N E 215 163 699 95 L F 230 168 70596 L G 274 174 737 100 H H 275 181 726 99 H

Example 15—Comparative Example

Sheets consisting of Kelvx 201 were produced using a 3.5 inch singlescrew extruder. Kelvx is a blend consisting of 69.85% PCTG (Eastar fromEastman Chemical Co. having 100 mole % terephthalic acid residues, 62mole % 1,4-cyclohexanedimethanol residues, and 38 mole % ethylene glycolresidues); 30% PC (bisphenol A polycarbonate); and 0.15% Weston 619(stabilizer sold by Crompton Corporation). A sheet was extrudedcontinuously, gauged to a thickness of 177 mil and then various sheetswere sheared to size. The glass transition temperature was measured onone sheet and was 100° C. Sheets were then conditioned at 50% relativehumidity and 60° C. for 2 weeks. Sheets were subsequently thermoformedinto a female mold having a draw ratio of 2.5:1 using a Brownthermoforming machine. The thermoforming oven heaters were set to70/60/60% output using top heat only. Sheets were left in the oven forvarious amounts of time in order to determine the effect of sheettemperature on the part quality as shown in the table below. Partquality was determined by measuring the volume of the thermoformed part,calculating the draw, and visually inspecting the thermoformed part. Thedraw was calculated as the part volume divided by the maximum partvolume achieved in this set of experiments (Example E). The thermoformedpart was visually inspected for any blisters and the degree ofblistering rated as none (N), low (L), or high (H). The results belowdemonstrate that these thermoplastic sheets with a glass transitiontemperature of 100° C. can be thermoformed under the conditions shownbelow, as evidenced by the production of sheets having at least 95% drawand no blistering, without predrying the sheets prior to thermoforming.Thermoforming Conditions Part Quality Sheet Part Heat Time TemperatureVolume Blisters Example (s) (° C.) (mL) Draw (%) (N, L, H) A 90 146 58275 N B 101 150 644 83 N C 111 154 763 98 N D 126 159 733 95 N E 126 159775 100 N F 141 165 757 98 N G 148 168 760 98 L

Example 16—Comparative Example

Sheets consisting of Kelvx 201 were produced using a 3.5 inch singlescrew extruder. A sheet was extruded continuously, gauged to a thicknessof 177 mil and then various sheets were sheared to size. The glasstransition temperature was measured on one sheet and was 100° C. Sheetswere then conditioned at 100% relative humidity and 25° C. for 2 weeks.Sheets were subsequently thermoformed into a female mold having a drawratio of 2.5:1 using a Brown thermoforming machine. The thermoformingoven heaters were set to 60/40/40% output using top heat only. Sheetswere left in the oven for various amounts of time in order to determinethe effect of sheet temperature on the part quality as shown in thetable below. Part quality was determined by measuring the volume of thethermoformed part, calculating the draw, and visually inspecting thethermoformed part. The draw was calculated as the part volume divided bythe maximum part volume achieved in this set of experiments (Example H).The thermoformed part was visually inspected for any blisters and thedegree of blistering rated as none (N), low (L), or high (H). Theresults below demonstrate that these thermoplastic sheets with a glasstransition temperature of 100° C. can be thermoformed under theconditions shown below, as evidenced by the production of sheets havinggreater than 95% draw and no blistering, without predrying the sheetsprior to thermoforming. Thermoforming Conditions Part Quality Sheet PartHeat Time Temperature Volume Blisters Example (s) (° C.) (mL) Draw (%)(N, L, H) A 110 143 185 25 N B 145 149 529 70 N C 170 154 721 95 N D 175156 725 96 N E 185 157 728 96 N F 206 160 743 98 L G 253 NR 742 98 H H261 166 756 100 HNR = Not recorded

Example 17—Comparative Example

Sheets consisting of PCTG 25976 (100 mole % terephthalic acid residues,62 mole % 1,4-cyclohexanedimethanol residues, and 38 mole % ethyleneglycol residues) were produced using a 3.5 inch single screw extruder. Asheet was extruded continuously, gauged to a thickness of 118 mil andthen various sheets were sheared to size. The glass transitiontemperature was measured on one sheet and was 87° C. Sheets were thenconditioned at 50% relative humidity and 60° C. for 4 weeks. Themoisture level was measured to be 0.17 wt %. Sheets were subsequentlythermoformed into a female mold having a draw ratio of 2.5:1 using aBrown thermoforming machine. The thermoforming oven heaters were set to70/60/60% output using top heat only. Sheets were left in the oven forvarious amounts of time in order to determine the effect of sheettemperature on the part quality as shown in the table below. Partquality was determined by measuring the volume of the thermoformed part,calculating the draw, and visually inspecting the thermoformed part. Thedraw was calculated as the part volume divided by the maximum partvolume achieved in this set of experiments (Example A). The thermoformedpart was visually inspected for any blisters and the degree ofblistering rated as none (N), low (L), or high (H). The results belowdemonstrate that these thermoplastic sheets with a glass transitiontemperature of 87° C. can be thermoformed under the conditions shownbelow, as evidenced by the production of sheets having greater than 95%draw and no blistering, without predrying the sheets prior tothermoforming. Thermoforming Conditions Part Quality Sheet Part HeatTime Temperature Volume Blisters Example (s) (° C.) (mL) Draw (%) (N, L,H) A 102 183 816 100 N B 92 171 811 99 N C 77 160 805 99 N D 68 149 80499 N E 55 143 790 97 N F 57 138 697 85 N

Example 18—Comparative Example

A miscible blend consisting of 20 wt % Teijin L-1250 polycarbonate (abisphenol-A polycarbonate), 79.85 wt % PCTG 25976, and 0.15 wt % Weston619 was produced using a 1.25 inch single screw extruder. Sheetsconsisting of the blend were then produced using a 3.5 inch single screwextruder. A sheet was extruded continuously, gauged to a thickness of118 mil and then various sheets were sheared to size. The glasstransition temperature was measured on one sheet and was 94° C. Sheetswere then conditioned at 50% relative humidity and 60° C. for 4 weeks.The moisture level was measured to be 0.25 wt %. Sheets weresubsequently thermoformed into a female mold having a draw ratio of2.5:1 using a Brown thermoforming machine. The thermoforming ovenheaters were set to 70/60/60% output using top heat only. Sheets wereleft in the oven for various amounts of time in order to determine theeffect of sheet temperature on the part quality as shown in the tablebelow. Part quality was determined by measuring the volume of thethermoformed part, calculating the draw, and visually inspecting thethermoformed part. The draw was calculated as the part volume divided bythe maximum part volume achieved in this set of experiments (Example A).The thermoformed part was visually inspected for any blisters and thedegree of blistering rated as none (N), low (L), or high (H). Theresults below demonstrate that these thermoplastic sheets with a glasstransition temperature of 94° C. can be thermoformed under theconditions shown below, as evidenced by the production of sheets havinggreater than 95% draw and no blistering, without predrying the sheetsprior to thermoforming. Thermoforming Conditions Part Quality Sheet PartHeat Time Temperature Volume Blisters Example (s) (° C.) (mL) Draw (%)(N, L, H) A 92 184 844 100 H B 86 171 838 99 N C 73 160 834 99 N D 58143 787 93 N E 55 143 665 79 N

Example 19—Comparative Example

A miscible blend consisting of 30 wt % Teijin L-1250 polycarbonate,69.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was produced using a1.25 inch single screw extruder. Sheets consisting of the blend werethen produced using a 3.5 inch single screw extruder. A sheet wasextruded continuously, gauged to a thickness of 118 mil and then varioussheets were sheared to size. The glass transition temperature wasmeasured on one sheet and was 99° C. Sheets were then conditioned at 50%relative humidity and 60° C. for 4 weeks. The moisture level wasmeasured to be 0.25 wt %. Sheets were subsequently thermoformed into afemale mold having a draw ratio of 2.5:1 using a Brown thermoformingmachine. The thermoforming oven heaters were set to 70/60/60% outputusing top heat only. Sheets were left in the oven for various amounts oftime in order to determine the effect of sheet temperature on the partquality as shown in the table below. Part quality was determined bymeasuring the volume of the thermoformed part, calculating the draw, andvisually inspecting the thermoformed part. The draw was calculated asthe part volume divided by the maximum part volume achieved in this setof experiments (Example A). The thermoformed part was visually inspectedfor any blisters and the degree of blistering rated as none (N), low(L), or high (H). The results below demonstrate that these thermoplasticsheets with a glass transition temperature of 99° C. can be thermoformedunder the conditions shown below, as evidenced by the production ofsheets having greater than 95% draw and no blistering, without predryingthe sheets prior to thermoforming. Thermoforming Conditions Part QualitySheet Part Heat Time Temperature Volume Blisters Example (s) (° C.) (mL)Draw (%) (N, L, H) A 128 194 854 100 H B 98 182 831 97 L C 79 160 821 96N D 71 149 819 96 N E 55 145 785 92 N F 46 143 0 0 NA G 36 132 0 0 NANA = not applicable.A value of zero indicates that the sheet was not formed because it didnot pull into the mold (likely because it was too cold).

Example 20—Comparative Example

A miscible blend consisting of 40 wt % Teijin L-1250 polycarbonate,59.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was produced using a1.25 inch single screw extruder. Sheets consisting of the blend werethen produced using a 3.5 inch single screw extruder. A sheet wasextruded continuously, gauged to a thickness of 118 mil and then varioussheets were sheared to size. The glass transition temperature wasmeasured on one sheet and was 105° C. Sheets were then conditioned at50% relative humidity and 60° C. for 4 weeks. The moisture level wasmeasured to be 0.265 wt %. Sheets were subsequently thermoformed into afemale mold having a draw ratio of 2.5:1 using a Brown thermoformingmachine. The thermoforming oven heaters were set to 70/60/60% outputusing top heat only. Sheets were left in the oven for various amounts oftime in order to determine the effect of sheet temperature on the partquality as shown in the table below. Part quality was determined bymeasuring the volume of the thermoformed part, calculating the draw, andvisually inspecting the thermoformed part. The draw was calculated asthe part volume divided by the maximum part volume achieved in this setof experiments (Examples 8A to 8E). The thermoformed part was visuallyinspected for any blisters and the degree of blistering rated as none(N), low (L), or high (H). The results below demonstrate that thesethermoplastic sheets with a glass transition temperature of 105° C. canbe thermoformed under the conditions shown below, as evidenced by theproduction of sheets having greater than 95% draw and no blistering,without predrying the sheets prior to thermoforming. ThermoformingConditions Part Quality Sheet Part Heat Time Temperature Volume BlistersExample (s) (° C.) (mL) Draw (%) (N, L, H) A 111 191 828 100 H B 104 182828 100 H C 99 179 827 100 N D 97 177 827 100 N E 78 160 826 100 N F 68149 759 92 N G 65 143 606 73 N

Example 21—Comparative Example

A miscible blend consisting of 50 wt % Teijin L-1250 polycarbonate,49.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was produced using a1.25 inch single screw extruder. A sheet was extruded continuously,gauged to a thickness of 118 mil and then various sheets were sheared tosize. The glass transition temperature was measured on one sheet and was111° C. Sheets were then conditioned at 50% relative humidity and 60° C.for 4 weeks. The moisture level was measured to be 0.225 wt %. Sheetswere subsequently thermoformed into a female mold having a draw ratio of2.5:1 using a Brown thermoforming machine. The thermoforming ovenheaters were set to 70/60/60% output using top heat only. Sheets wereleft in the oven for various amounts of time in order to determine theeffect of sheet temperature on the part quality as shown in the tablebelow. Part quality was determined by measuring the volume of thethermoformed part, calculating the draw, and visually inspecting thethermoformed part. The draw was calculated as the part volume divided bythe maximum part volume achieved in this set of experiments (Examples Ato D). The thermoformed part was visually inspected for any blisters andthe degree of blistering rated as none (N), low (L), or high (H). Theresults below demonstrate that these thermoplastic sheets with a glasstransition temperature of 111° C. can be thermoformed under theconditions shown below, as evidenced by the production of sheets havinggreater than 95% draw and no blistering, without predrying the sheetsprior to thermoforming. Thermoforming Conditions Part Quality Sheet PartHeat Time Temperature Volume Blisters Example (s) (° C.) (mL) Draw (%)(N, L, H) A 118 192 815 100 H B 99 182 815 100 H C 97 177 814 100 L D 87171 813 100 N E 80 160 802 98 N F 64 154 739 91 N G 60 149 0 0 NANA = not applicable.A value of zero indicates that the sheet was not formed because it didnot pull into the mold (likely because it was too cold).

Example 22—Comparative Example

A miscible blend consisting of 60 wt % Teijin L-1250 polycarbonate,39.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was produced using a1.25 inch single screw extruder. Sheets consisting of the blend werethen produced using a 3.5 inch single screw extruder. A sheet wasextruded continuously, gauged to a thickness of 118 mil and then varioussheets were sheared to size. The glass transition temperature wasmeasured on one sheet and was 117° C. Sheets were then conditioned at50% relative humidity and 60° C. for 4 weeks. The moisture level wasmeasured to be 0.215 wt %. Sheets were subsequently thermoformed into afemale mold having a draw ratio of 2.5:1 using a Brown thermoformingmachine. The thermoforming oven heaters were set to 70/60/60% outputusing top heat only. Sheets were left in the oven for various amounts oftime in order to determine the effect of sheet temperature on the partquality as shown in the table below. Part quality was determined bymeasuring the volume of the thermoformed part, calculating the draw, andvisually inspecting the thermoformed part. The draw was calculated asthe part volume divided by the maximum part volume achieved in this setof experiments (Example A). The thermoformed part was visually inspectedfor any blisters and the degree of blistering rated as none (N), low(L), or high (H). The results below demonstrate that these thermoplasticsheets with a glass transition temperature of 117° C. cannot bethermoformed under the conditions shown below, as evidenced by theinability to produce sheets having greater than 95% draw and noblistering, without predrying the sheets prior to thermoforming.Thermoforming Conditions Part Quality Sheet Part Heat Time TemperatureVolume Blisters Example (s) (° C.) (mL) Draw (%) (N, L, H) A 114 196 813100 H B 100 182 804 99 H C 99 177 801 98 L D 92 171 784 96 L E 82 168727 89 L F 87 166 597 73 N

Example 23—Comparative Example

A miscible blend consisting of 65 wt % Teijin L-1250 polycarbonate,34.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was produced using a1.25 inch single screw extruder. Sheets consisting of the blend werethen produced using a 3.5 inch single screw extruder. A sheet wasextruded continuously, gauged to a thickness of 118 mil and then varioussheets were sheared to size. The glass transition temperature wasmeasured on one sheet and was 120° C. Sheets were then conditioned at50% relative humidity and 60° C. for 4 weeks. The moisture level wasmeasured to be 0.23 wt %. Sheets were subsequently thermoformed into afemale mold having a draw ratio of 2.5:1 using a Brown thermoformingmachine. The thermoforming oven heaters were set to 70/60/60% outputusing top heat only. Sheets were left in the oven for various amounts oftime in order to determine the effect of sheet temperature on the partquality as shown in the table below. Part quality was determined bymeasuring the volume of the thermoformed part, calculating the draw, andvisually inspecting the thermoformed part. The draw was calculated asthe part volume divided by the maximum part volume achieved in this setof experiments (Example A). The thermoformed part was visually inspectedfor any blisters and the degree of blistering rated as none (N), low(L), or high (H). The results below demonstrate that these thermoplasticsheets with a glass transition temperature of 120° C. cannot bethermoformed under the conditions shown below, as evidenced by theinability to produce sheets having greater than 95% draw and noblistering, without predrying the sheets prior to thermoforming.Thermoforming Conditions Part Quality Sheet Part Heat Time TemperatureVolume Blisters Example (s) (° C.) (mL) Draw (%) (N, L, H) A 120 197 825100 H B 101 177 820 99 H C 95 174 781 95 L D 85 171 727 88 L E 83 166558 68 L

Example 24—Comparative Example

A miscible blend consisting of 70 wt % Teijin L-1250 polycarbonate,29.85 wt % PCTG 25976, and 0.15 wt % Weston 619 was produced using a1.25 inch single screw extruder. Sheets consisting of the blend werethen produced using a 3.5 inch single screw extruder. A sheet wasextruded continuously, gauged to a thickness of 118 mil and then varioussheets were sheared to size. The glass transition temperature wasmeasured on one sheet and was 123° C. Sheets were then conditioned at50% relative humidity and 60° C. for 4 weeks. The moisture level wasmeasured to be 0.205 wt %. Sheets were subsequently thermoformed into afemale mold having a draw ratio of 2.5:1 using a Brown thermoformingmachine. The thermoforming oven heaters were set to 70/60/60% outputusing top heat only. Sheets were left in the oven for various amounts oftime in order to determine the effect of sheet temperature on the partquality as shown in the table below. Part quality was determined bymeasuring the volume of the thermoformed part, calculating the draw, andvisually inspecting the thermoformed part. The draw was calculated asthe part volume divided by the maximum part volume achieved in this setof experiments (Examples A and B). The thermoformed part was visuallyinspected for any blisters and the degree of blistering rated as none(N), low (L), or high (H). The results below demonstrate that thesethermoplastic sheets with a glass transition temperature of 123° C.cannot be thermoformed under the conditions shown below, as evidenced bythe inability to produce sheets having greater than 95% draw and noblistering, without predrying the sheets prior to thermoforming.Thermoforming Conditions Part Quality Sheet Part Heat Time TemperatureVolume Blisters Example (s) (° C.) (mL) Draw (%) (N, L, H) A 126 198 826100 H B 111 188 822 100 H C 97 177 787 95 L D 74 166 161 19 L E 58 154 00 NA F 48 149 0 0 NANA = not applicable.A value of zero indicates that the sheet was not formed because it didnot pull into the mold (likely because it was too cold).

Example 25—Comparative Example

Sheets consisting of Teijin L-1250 polycarbonate were produced using a3.5 inch single screw extruder. A sheet was extruded continuously,gauged to a thickness of 118 mil and then various sheets were sheared tosize. The glass transition temperature was measured on one sheet and was149° C. Sheets were then conditioned at 50% relative humidity and 60° C.for 4 weeks. The moisture level was measured to be 0.16 wt %. Sheetswere subsequently thermoformed into a female mold having a draw ratio of2.5:1 using a Brown thermoforming machine. The thermoforming ovenheaters were set to 70/60/60% output using top heat only. Sheets wereleft in the oven for various amounts of time in order to determine theeffect of sheet temperature on the part quality as shown in the tablebelow. Part quality was determined by measuring the volume of thethermoformed part, calculating the draw and visually inspecting thethermoformed part. The draw was calculated as the part volume divided bythe maximum part volume achieved in this set of experiments (Example A).The thermoformed part was visually inspected for any blisters and thedegree of blistering rated as none (N), low (L), or high (H). Theresults below demonstrate that these thermoplastic sheets with a glasstransition temperature of 149° C. cannot be thermoformed under theconditions shown below, as evidenced by the inability to produce sheetshaving greater than 95% draw and no blistering, without predrying thesheets prior to thermoforming. Thermoforming Conditions Part QualitySheet Part Heat Time Temperature Volume Blisters Example (s) (° C.) (mL)Draw (%) (N, L, H) A 152 216 820 100 H B 123 193 805 98 H C 113 191 17922 H D 106 188 0 0 H E 95 182 0 0 NA F 90 171 0 0 NANA = not applicable.A value of zero indicates that the sheet was not formed because it didnot pull into the mold (likely because it was too cold).It can be clearly seen from a comparison of the data in the aboverelevant working examples that the polyesters of the present inventionoffer a definite advantage over the commercially available polyesterswith regard to glass transition temperature, density, slowcrystallization rate, melt viscosity, and toughness.

Example 24A coating composition was formed by mixing an epoxy-functionalpolysiloxane with a UV curing additive. The silicone used was availableas General Electric 9300 silicone release agent, and the UV curing agentused was General Electric UV9380c. 50 grams of the silicone coating wasstirred with 1 gram of the UV curing agent until uniformly mixed. Thiscoating was applied to an amorphous extruded polyethylene terephthalatefilm. The coated film was passed into a UV curing apparatus (AmericanUltraviolet mini conveyorized UV cure system) at 50 feet per minute at apower density setting of 200 watts per inch.

Additionally, extruded films of polyethylene, polystyrene, PCTG, PETGand cellulose acetate were examined uncoated.

Biocompatibility was determined by measuring the adsorption of proteinfrom solution. The samples were first sonicated in water for 10 minutes,followed by pretreatment in phosphate buffer for 24 hours. The sampleswere then immersed for 30 minutes in a 0.1 mg/mL solution of bovinefibrinogen, removed and immersed for 30 minutes in clean phosphatebuffer solution. The samples were removed from the buffer, rinsed withdeionized water, and dried in vacuum for 24 hours. These samples wereexamined for surface atomic composition using X-ray photoelectronspectroscopy (XPS). Because the fibrinogen contains nitrogen and thesubstrate polymers do not, the quantity of nitrogen detected at thesurface is proportional to the propensity for the surface to accumulateor adsorb proteins. It is this adsorption of proteins at the surfacethat controls the interaction of a biological system with a surface.Substrate % surface nitrogen PET 5.3 Copolyester “PETG” 6.6 Copolyester“PCTG” 5.6 Cellulose Acetate 4.7 Polypropylene 3.1 Silicone-coated PET0.3

As seen from the results above, coatings of UV-cured silicone materialson polymer substrates can substantially decrease the amount offibrinogen adsorbed onto surfaces as evidenced by a lower indicated %surface nitrogen.

1. A medical device comprising: (1) a UV-cured silicone polymer coatingon at least a portion of a surface of the device; and (2) at least onepolyester composition comprising at least one polyester which comprises:(a) a dicarboxylic acid component comprising: i) 70 to 100 mole % ofterephthalic acid residues; ii) 0 to 30 mole % of aromatic dicarboxylicacid residues having up to 20 carbon atoms; and iii) 0 to 10 mole % ofaliphatic dicarboxylic acid residues having up to 16 carbon atoms; and(b) a glycol component comprising: i) 1 to 99 mole % of2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and ii) 1 to 99 mole %of 1,4-cyclohexanedimethanol residues, wherein the total mole % of thedicarboxylic acid component is 100 mole %, and the total mole % of theglycol component is 100 mole %; and wherein the inherent viscosity ofthe polyester is from 0.10 to 1.2 dL/g as determined in 60/40 (wt/wt)phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at 25° C.;and wherein the polyester has a Tg of from 85 to 200° C.
 2. A medicaldevice comprising: (1) a UV-cured silicone polymer coating on at least aportion of a surface of the device; and (2) at least one polyestercomposition comprising at least one polyester which comprises: (a) adicarboxylic acid component comprising: i) 70 to 100 mole % ofterephthalic acid residues; ii) 0 to 30 mole % of aromatic dicarboxylicacid residues having up to 20 carbon atoms; and iii) 0 to 10 mole % ofaliphatic dicarboxylic acid residues having up to 16 carbon atoms; and(b) a glycol component comprising: i) 40 to 65 mole % of2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and ii) 35 to 60 mole% of 1,4-cyclohexanedimethanol residues, wherein the total mole % of thedicarboxylic acid component is 100 mole %, and the total mole % of theglycol component is 100 mole %; and wherein the inherent viscosity ofthe polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at 25° C.;and wherein the polyester has a Tg of 85 to 200° C.
 3. A medical devicecomprising: (1) a UV-cured silicone polymer coating on at least aportion of a surface of the device; and (2) at least one polyestercomposition comprising at least one polyester which comprises: (a) adicarboxylic acid component comprising: i) 70 to 100 mole % ofterephthalic acid residues; ii) 0 to 30 mole % of aromatic dicarboxylicacid residues having up to 20 carbon atoms; and iii) 0 to 10 mole % ofaliphatic dicarboxylic acid residues having up to 16 carbon atoms; and(b) a glycol component comprising: i) 40 to 80 mole % of2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and ii) 20 to 60 mole% of 1,4-cyclohexanedimethanol residues, wherein the total mole % of thedicarboxylic acid component is 100 mole %, and the total mole % of theglycol component is 100 mole %; and wherein the inherent viscosity ofthe polyester is from 0.35 to 1.2 dL/g as determined in 60/40 (wt/wt)phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at 25° C.;and wherein the polyester has a Tg of 125 to 200° C.
 4. A medical devicecomprising: (1) a UV-cured silicone polymer coating on at least aportion of a surface of the device; and (2) at least one polyester whichcomprises (a) a dicarboxylic acid component comprising: i) from 70 to100 mole % of terephthalic acid residues; ii) 0 to 30 mole % of aromaticdicarboxylic acid residues having up to 20 carbon atoms; and iii) 0 to10 mole % of aliphatic dicarboxylic acid residues having up to 16 carbonatoms; and (b) a glycol component comprising: i) 15 to 70 mole % of2,2,4,4-tetramethyl-1,3-cyclobutanediol residues; and ii) 30 to 85 mole% of 1,4-cyclohexanedimethanol residues, wherein the total mole % of thedicarboxylic acid component is 100 mole %, and the total mole % of theglycol component is 100 mole %; and wherein the inherent viscosity ofthe polyester is from 0.5 to 1.2 dL/g as determined in 60/40 (wt/wt)phenol/tetrachloroethane at a concentration of 0.5 g/100 ml at 25° C. 5.The device of claim 1, wherein the coating comprises an epoxy-functionalpolysiloxane and a UV curing agent.
 6. The device of claim 1, furthercomprising a patterned surface defined by the coating.
 7. The device ofclaim 1, wherein at least a portion of the surface of device is proteinresistant.
 8. The device of claim 1, wherein said polyester has a Tg of110 to 200° C.
 9. The device of claims 1, wherein said polyester has aTg of 110 to 170° C.
 10. The device of claim 1, wherein said polyesterhas a Tg of 110 to 160° C.
 11. The device of claim 1, wherein saidpolyester has a Tg of 110 to 150° C.
 12. The device of claim 1, whereinsaid polyester has a Tg of 110 to 130° C.
 13. The device of claim 1,wherein said polyester has a Tg of 120 to 160° C.
 14. The device ofclaim 1, wherein said polyester has a Tg of 120 to 150° C.
 15. Thedevice of claim 1, wherein said polyester has a Tg of 130 to 160° C. 16.The device of claim 1, wherein said polyester has a Tg of 130 to 150° C.17. The device of claim 1, wherein said polyester has a Tg of 130 to145° C.
 18. The device of claim 1, wherein said polyester has a Tg of140 to 150° C.
 19. The device of claim 1, wherein said polyester has aTg of 135 to 145° C.
 20. The device of claim 1, wherein the glycolcomponent of said polyester comprises 40 to 64.9 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 35.1 to 60 mole %1,4-cyclohexanedimethanol.
 21. The device of claim 1, wherein the glycolcomponent of said polyester comprises 40 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 60 mole %1,4-cyclohexanedimethanol.
 22. The device of claim 1, wherein the glycolcomponent of said polyester comprises 45 to 60 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 40 to 55 mole %1,4-cyclohexanedimethanol.
 23. The device of claim 1, wherein the glycolcomponent of said polyester comprises 45 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to 55 mole %1,4-cyclohexanedimethanol.
 24. The device of claim 1, wherein the glycolcomponent of said polyester comprises 46 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to less than 55 mole %1,4-cyclohexanedimethanol.
 25. The device of claim 1, wherein the glycolcomponent of said polyester comprises 46 to 55 mole %2,2,4,4-tetramethyl-1,3-cyclobutanediol and 45 to less than 55 mole %1,4-cyclohexanedimethanol.
 26. The device of claim 1, wherein thedicarboxylic acid component comprises 80 to 100 mole % of terephthalicacid, an ester thereof, or a mixture thereof.
 27. The device of claim 1,wherein the dicarboxylic acid component comprises 90 to 100 mole % ofterephthalic acid, an ester thereof, or a mixture thereof.
 28. Thedevice of claim 1, wherein the dicarboxylic acid component comprises 95to 100 mole % of terephthalic acid, an ester thereof, or a mixturethereof.
 29. The device of claim 1, wherein said polyester comprises1,3-propanediol, 1,4-butanediol, or mixtures thereof.
 30. The device ofclaim 1, wherein said polyester comprises less than 15 mole % ofresidues from at least one modifying glycol.
 31. The device of claim 1,wherein said polyester comprises less than 15 mole % of ethylene glycolresidues.
 32. The device of claim 1, wherein said polyester comprises2,2,4,4-tetramethyl-1,3-cyclobutanediol in the pure cis form, the puretrans form, or mixtures of the cis and trans forms.
 33. The device ofclaim 1, wherein said 2,2,4,4-tetramethyl-1,3-cyclobutanediol is amixture comprising greater than 50 mole % ofcis-2,2,4,4-tetramethyl-1,3-cyclobutanediol and less than 50 mole % oftrans-2,2,4,4-tetramethyl-1,3-cyclobutanediol.
 34. The device of claim1, wherein said 2,2,4,4-tetramethyl-1,3-cyclobutanediol is a mixturecomprising greater than 55 mole % ofcis-2,2,4,4-tetramethyl-1,3-cyclobutanediol and less than 45 mole % oftrans-2,2,4,4-tetramethyl-1,3-cyclobutanediol.
 35. The device of claim1, wherein said 2,2,4,4-tetramethyl-1,3-cyclobutanediol is a mixturecomprising greater than 70 mole % ofcis-2,2,4,4-tetramethyl-1,3-cyclobutanediol and less than 30 mole % oftrans-2,2,4,4-tetramethyl-1,3-cyclobutanediol.
 36. The device of claim1, wherein said 2,2,4,4-tetramethyl-1,3-cyclobutanediol is a mixturecomprising 30 to 70 mole % oftrans-2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 70 mole % ofcis-2,2,4,4-tetramethyl-1,3-cyclobutanediol.
 37. The device of claim 1,wherein said 2,2,4,4-tetramethyl-1,3-cyclobutanediol is a mixturecomprising 50 to 70 mole % oftrans-2,2,4,4-tetramethyl-1,3-cyclobutanediol and 30 to 50 mole % ofcis-2,2,4,4-tetramethyl-1,3-cyclobutanediol.
 38. The device of claim 1,wherein said polyester composition comprises at least one polymer chosenfrom poly(amides), poly(etherimides), polyphenylene oxides,poly(phenylene oxide)/polystyrene blends, polystyrene resins,polyphenylene sulfides, polyphenylene sulfide/sulfones,poly(ester-carbonates), polycarbonates, polysulfones; polysulfoneethers, and poly(ether-ketones).
 39. The device of claim 1, wherein saidpolyester comprises a branching agent for the polyester.
 40. The deviceof claim 1, wherein said polyester is linear.
 41. The device of claim 1,wherein said polyester composition comprises at least one polycarbonate.42. The device of claim 1, wherein said polyester comprises a branchingagent for the polycarbonate.
 43. The device of claim 1, wherein saidpolyester comprises a branching agent in an amount of 0.01 to 10 weight% based on the total weight of the polyester.
 44. The device of claim 1,wherein said polyester comprises a branching agent in an amount of 0.01to 5 weight % based on the total weight of the polyester.
 45. The deviceof claim 1, wherein the melt viscosity of said polyester is less than30,000 poise as measured at 1 radian/second on a rotary melt rheometerat 290° C.
 46. The device of claim 1, wherein the melt viscosity of saidpolyester is less than 20,000 poise as measured at 1 radian/second on arotary melt rheometer at 290° C.
 47. The device of claim 1, wherein saidpolyester has a crystallization half-time greater than 5 minutes at 170°C.
 48. The device of claim 1, wherein said polyester has acrystallization half-time of greater than 1,000 minutes at 170° C. 49.The device of claim 1, wherein said polyester has a crystallizationhalf-time of greater than 10,000 minutes at 170° C.
 50. The device ofclaim 1, wherein said polyester composition has a density of less than1.2 g/ml at 23° C.
 51. The device of claim 1, wherein said polyestercomposition has a density of less than 1.18 g/ml at 23° C.
 52. Thedevice of claim 1, wherein said polyester composition comprises at leastone thermal stabilizer or reaction products thereof.
 53. The device ofclaim 1, wherein the yellowness index of said polyester according toASTM D-1925 is less than
 50. 54. The device of claim 1, wherein the b*value of said polyester is from 0 to less than
 10. 55. The device ofclaim 1, wherein the L* value of said polyester is from 50 to
 90. 56.The device of claim 1, wherein the b* value of said polyester is from 0to less than 10 and the L* value of said polyester is from 50 to
 90. 57.The device of claim 1, wherein said polyester has a notched Izod impactstrength of at least 3 ft-lbs/in at 23° C. according to ASTM D256 with a10-mil notch in a ⅛-inch thick bar.
 58. The device of claim 1, whereinsaid polyester has a notched Izod impact strength of at least 10ft-lbs/in at 23° C. according to ASTM D256 with a 10-mil notch in a⅛-inch thick bar.
 59. The device of claim 1, wherein the polyestercomprises at least one catalyst comprising a tin compound or a reactionproduct thereof and/or residues thereof.
 60. The device of claim 1,wherein the polyester comprises at least one chain extender.
 61. Thedevice of claim 1, wherein the polyester comprises an additive chosenfrom at least one of the following: colorants, dyes, mold releaseagents, flame retardants, plasticizers, nucleating agents, UVstabilizers, thermal stabilizers and/or reaction products thereof,fillers, and impact modifiers.
 62. A method for reducing interactionbetween the medical device of claim 1 and a biological fluid or system,said method comprising: coating at least a portion of a surface of thedevice with a UV-curable silicone polymer composition; and exposing atleast a portion of said UV-curable silicone polymer composition toultraviolet light to cure the composition.
 63. The method of claim 62,wherein the silicone polymer composition comprises an epoxy-functionalpolysiloxane and a UV curing agent.
 64. The method of claim 63, furthercomprising: removing any uncured silicone polymer composition from thesurface of the device to produce a patterned surface comprising areas ofrelatively low protein binding and relatively high protein binding. 65.The method of claim 64, wherein the curing time is 5 seconds or less.